WO2024060314A1 - Medical treatment device and treatment probe - Google Patents

Medical treatment device and treatment probe Download PDF

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Publication number
WO2024060314A1
WO2024060314A1 PCT/CN2022/123856 CN2022123856W WO2024060314A1 WO 2024060314 A1 WO2024060314 A1 WO 2024060314A1 CN 2022123856 W CN2022123856 W CN 2022123856W WO 2024060314 A1 WO2024060314 A1 WO 2024060314A1
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WO
WIPO (PCT)
Prior art keywords
probe
litt
laser
lens
target object
Prior art date
Application number
PCT/CN2022/123856
Other languages
French (fr)
Chinese (zh)
Inventor
崔小飞
符钰棋
纳西尔 古尔扎里 穆罕默德
陈士行
陈默扬
王引言
王鹏
朱磊
李胜中
Original Assignee
上海超光微医疗科技有限公司
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from CN202211151254.4A external-priority patent/CN117770947A/en
Priority claimed from CN202211159480.7A external-priority patent/CN117338407A/en
Priority claimed from CN202211156542.9A external-priority patent/CN117530770A/en
Application filed by 上海超光微医疗科技有限公司 filed Critical 上海超光微医疗科技有限公司
Priority to US17/980,409 priority Critical patent/US20240000507A1/en
Priority to US17/980,444 priority patent/US20240001487A1/en
Publication of WO2024060314A1 publication Critical patent/WO2024060314A1/en

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16H—GEARING
    • F16H27/00—Step-by-step mechanisms without freewheel members, e.g. Geneva drives
    • F16H27/02—Step-by-step mechanisms without freewheel members, e.g. Geneva drives with at least one reciprocating or oscillating transmission member
    • G—PHYSICS
    • G05—CONTROLLING; REGULATING
    • G05D—SYSTEMS FOR CONTROLLING OR REGULATING NON-ELECTRIC VARIABLES
    • G05D23/00—Control of temperature
    • G05D23/19—Control of temperature characterised by the use of electric means
    • G05D23/20—Control of temperature characterised by the use of electric means with sensing elements having variation of electric or magnetic properties with change of temperature

Definitions

  • the present invention relates to the field of medical diagnosis and treatment, and in particular to a medical treatment device and a treatment probe.
  • Laser interstitial thermotherapy is a treatment method that uses the thermal effect of laser to destroy target tissue. It is also the latest minimally invasive surgery for the treatment of brain tumors.
  • the basic principle is to use the stereotactic method in neurosurgery to insert an optical fiber probe with a cooling circulation sleeve into the patient's brain lesion. During treatment, the laser reaches the probe through the optical fiber, thereby heating the lesion tissue around the probe. achieve the purpose of ablation.
  • MRg magnetic resonance-guided
  • the current LITT system has the following problems: (1) Magnetic resonance thermal imaging (MRTI) is used to measure the temperature of the distal and surrounding ablation target lesions of the LITT probe system. Due to the long distance from the target lesion, MRTI temperature measurement is difficult to guarantee. The accuracy of real-time temperature control and detection often requires additional algorithm estimation for non-real-time compensation, which usually has hysteretic subjectivity in algorithm theory, making it difficult to quantify and avoid thermal damage to surrounding healthy tissue; (2) High-power LITT As the core structure of the LITT probe, the diffusion applicator is not uniform enough in manufacturing process, and the physical scattering units are too concentrated.
  • MRTI Magnetic resonance thermal imaging
  • the medical treatment device includes: a magnetic resonance imaging (MRI) device configured to image a specific area including a target object and generate a magnetic resonance image; a laser interstitial thermotherapy (LITT) device including: a LITT probe based on In the magnetic resonance image, the LITT probe is close to the target object and treats the target object by emitting laser; and a temperature measurement element is integrated with the LITT probe into an integrated probe, and the temperature measurement element is The element is configured to obtain the temperature of the target object.
  • MRI magnetic resonance imaging
  • LITT laser interstitial thermotherapy
  • the temperature measuring element includes a K-type thermocouple.
  • the K-type thermocouple is close to the target object to collect temperature changes of the target object in real time.
  • the temperature measurement element includes a fiber Bragg grating (FBG) sensor.
  • FBG fiber Bragg grating
  • MFD
  • the FBG sensor is close to the target object and determines a temperature change of the target object, wherein the temperature change of the target object is based on the acquired thermal sensitivity of the FBG and the thermal sensitivity of the FBG, S FSG , by The relationship between the wavelength drift ⁇ S and the temperature change ⁇ T is determined by calibration.
  • the relationship between the Bragg wavelength shift ⁇ S and the temperature change ⁇ T is obtained by placing the FBG sensor in a temperature controller, the temperature of the temperature controller changes intermittently, and at the same time, the amplified spontaneous The radiation (ASE) laser passes through the circulator and reaches the FBG sensor.
  • the reflection signal of the FBG sensor enters the telecommunications spectrum analyzer through the circulator.
  • the telecommunications spectrum analyzer monitors the reflection spectrum of the FBG sensor to determine .
  • the medical treatment device further includes an optical coherence tomography (OCT) device configured to image the target object and generate an OCT image.
  • OCT optical coherence tomography
  • the OCT device includes an OCT probe that emits a light signal to the target object to image the target object during treatment, and the OCT probe emits a light signal.
  • the optical signal has two different central wavelengths.
  • the OCT probe, the LITT probe and the temperature measurement element are integrated into the integrated probe.
  • the medical treatment device further includes: a driving device including: a translation cable and a rotation cable, and a translation control mechanism and a rotation control mechanism, wherein the translation cable and the rotation cable are respectively connected to The translation control mechanism and the rotation control mechanism, which are connected to the LITT probe, control the translation movement of the LITT probe respectively through the translation cable and the rotation cable. and rotational motion.
  • a driving device including: a translation cable and a rotation cable, and a translation control mechanism and a rotation control mechanism, wherein the translation cable and the rotation cable are respectively connected to The translation control mechanism and the rotation control mechanism, which are connected to the LITT probe, control the translation movement of the LITT probe respectively through the translation cable and the rotation cable. and rotational motion.
  • the translation control mechanism includes a worm gear assembly and a timing belt transmission assembly
  • the rotation control mechanism includes a timing belt transmission assembly
  • the LITT probe is a LITT lateral ablation probe or a LITT circumferential ablation probe.
  • the LITT lateral ablation probe includes: a probe body; and a coating covering the end surface of the probe body, wherein the end surface of the probe body and the axis of the probe body form a first angle, the probe body includes a needle core and a hard cladding located on the outer periphery of the needle core, and the coating is a noble metal target coating.
  • the plating layer has a double-layer structure, the layer close to the end surface of the probe body is pure silver, and the layer far away from the end surface of the probe body is silicon monoxide.
  • the LITT lateral ablation probe is obtained by smoothing the end surface of the probe body, and then covering the smoothed end surface with the coating by magnetron sputtering coating.
  • the LITT lateral ablation probe includes: a probe body; and a lens connected to an end surface of the probe body, wherein the end surface of the probe body is perpendicular to the axis of the probe body, so The lens has a first vertex angle, the probe body includes a needle core and a hard cladding located on the outer periphery of the needle core, and the lens is a sapphire lens.
  • the lens is a beveled cylindrical lens, or a beveled hemispherical or hemispherical lens.
  • the LITT lateral ablation probe is produced by smoothing the end surface of the probe body, welding the probe body and the lens, and performing fire polishing on the welded surface. owned.
  • the LITT circumferential ablation probe includes: a probe body, the probe body includes a conical surface, the conical surface is provided with grooves, the grooves are evenly distributed on the conical surface in a pattern, wherein the laser generated by the LITT probe is emitted from the grooves.
  • the diameter of the tapered surface gradually decreases from an initial diameter to a preset diameter, where the initial diameter is 630 ⁇ m, and the preset diameter is 100 ⁇ m.
  • the pattern includes a single thread shape, a cross-thread shape or a diamond grid shape or a combination thereof.
  • the tapered surface is formed by performing the following operations: fixing both ends of the tapered workpiece to be carved on the slide rail and the fixing device respectively; the laser controller controls the laser to emit laser, and the power of the laser is 30W, The wavelength is 10600nm.
  • the laser is attenuated to 6.6 to 11.2W by the laser power attenuator.
  • the attenuated laser is divided into two laser beams through the diffraction beam splitting lens unit.
  • the power of the two laser beams is equal.
  • the two laser beams pass through The focusing lens unit focuses on the surface of the workpiece to be carved into a cone; and the motion drive controller controls the motion driver to drive the movement of the workpiece to be carved into a cone.
  • the pattern-like grooves evenly distributed on the tapered surface are formed by performing the following operations: fixing both ends of the workpiece to be carved to the slide rail and the fixing device respectively; the laser controller controls the laser emission Laser, the power of the laser is 30W, the wavelength is 10600nm, the laser is focused to the surface of the workpiece to be carved through a lens group, the lens group includes a first concave lens, a first convex lens and a second concave lens, the third concave lens A concave lens and a first convex lens are used to expand the diameter of the laser beam to a first diameter, and the second concave lens is used to focus the laser beam of the first diameter onto the surface of the workpiece to be engraved to form a light spot, the diameter of the light spot is 45 ⁇ m; and movement The drive controller controls the motion driver to drive the movement of the workpiece to be carved.
  • the spatial intensity distribution of the laser emitted by the LITT circumferential ablation probe is obtained by obtaining the signal output by the laser measurement sensor and generating a specific orientation of the laser emitted by the LITT circumferential ablation probe.
  • Polarity intensity wherein the LITT circumferential ablation probe is connected to a helium-neon laser with a laser wavelength of 632.8nm, and a slit diaphragm is provided between the laser measurement sensor and the LITT circumferential ablation probe, so The slit size of the slit diaphragm is 0.3mm; and the motion drive controller controls the motion driver to drive the diaphragm and the laser measurement sensor to perform circumferential and axial movements along the tapered surface of the LITT circumferential ablation probe. to obtain the spatial intensity distribution of the laser light emitted by the LITT circumferential ablation probe, wherein the aperture and the laser measurement sensor are fixedly connected to the motion driver.
  • LITT laser interstitial thermal therapy
  • the LITT lateral ablation probe comprises a probe body; and a coating covering the end face of the probe body, wherein the end face of the probe body forms a first angle with the axis of the probe body, the probe body comprises a needle core and a hard cladding located on the outer periphery of the needle core, the needle core is made of pure silica material, the hard cladding is made of technology enhanced cladding silica (TECS) material, and the coating is a precious metal target coating.
  • LITT lateral ablation probe comprises a probe body; and a coating covering the end face of the probe body, wherein the end face of the probe body forms a first angle with the axis of the probe body, the probe body comprises a needle core and a hard cladding located on the outer periphery of the needle core, the needle core is made of pure silica material, the hard cladding is made of technology enhanced cladding silica (TECS) material, and the coating is a
  • the plating layer has a double-layer structure, the layer close to the end surface of the probe body is pure silver, and the layer far away from the end surface of the probe body is silicon monoxide.
  • the thickness of the layer close to the end face of the probe body is 100 nm
  • the thickness of the layer far away from the end face of the probe body is 150 nm
  • the plating layer and the axis of the probe body are at a second second angle.
  • the included angle is, and the second included angle is 47°.
  • the LITT lateral ablation probe is obtained by smoothing the end surface of the probe body, and then covering the smoothed end surface with the coating by magnetron sputtering coating.
  • LITT lateral ablation probe for LITT equipment, characterized in that the LITT lateral ablation probe includes: a probe body; and a probe connected to the A lens on the end face of the probe body, wherein the end face of the probe body is perpendicular to the axis of the probe body, the lens has a first vertex angle, the probe body includes a needle core and a hard package located on the outer periphery of the needle core layer, the needle core is made of pure silicon dioxide material, the hard cladding is made of TECS material, and the lens is a sapphire lens.
  • LITT lateral ablation probe includes: a probe body; and a probe connected to the A lens on the end face of the probe body, wherein the end face of the probe body is perpendicular to the axis of the probe body, the lens has a first vertex angle, the probe body includes a needle core and a hard package located on the outer periphery of the needle core layer, the needle core is made of pure silicon dioxide material, the hard
  • the lens is a beveled cylindrical lens, or a beveled hemispherical or semi-ellipsoidal lens.
  • the LITT lateral ablation probe is produced by smoothing the end surface of the probe body, welding the probe body and the lens, and performing fire polishing on the welded surface. owned.
  • LITT laser interstitial thermotherapy
  • the LITT probe circumferential ablation includes: a probe body, and the probe body It includes a tapered surface, and grooves are provided on the tapered surface. The grooves are evenly distributed on the tapered surface in a pattern, and the laser light generated by the LITT probe is emitted from the grooves.
  • the diameter of the tapered surface gradually decreases from an initial diameter to a preset diameter, where the initial diameter is 630 ⁇ m, and the preset diameter is 100 ⁇ m.
  • the pattern includes a single thread shape, a cross-thread shape or a diamond grid shape or a combination thereof.
  • the tapered surface is formed by performing the following operations: fixing both ends of the tapered workpiece to be carved on the slide rail and the fixing device respectively; the laser controller controls the laser to emit laser, and the power of the laser is 30W, The wavelength is 10600nm.
  • the laser is attenuated to 6.6 to 11.2W by the laser power attenuator.
  • the attenuated laser is divided into two laser beams through the diffraction beam splitting lens unit.
  • the power of the two laser beams is equal.
  • the two laser beams pass through The focusing lens unit focuses on the surface of the workpiece to be carved into a cone; and the motion drive controller controls the motion driver to drive the movement of the workpiece to be carved into a cone.
  • the grooves uniformly distributed on the conical surface in a pattern are formed by performing the following operations: fixing the two ends of the workpiece to be carved to a slide rail and a fixing device respectively; a laser controller controls the laser to emit a laser, the power of the laser is 30W, the wavelength is 10600nm, the laser is focused onto the surface of the workpiece to be carved through a lens group, the lens group includes a first concave lens, a first convex lens and a second concave lens, the first concave lens and the first convex lens are used to expand the diameter of the laser beam to a first diameter, the second concave lens is used to focus the laser beam of the first diameter onto the surface of the workpiece to be carved to form a light spot, the diameter of the light spot is 45 ⁇ m; and a motion drive controller controls the motion driver to drive the workpiece to be carved to move.
  • the spatial intensity distribution of the laser emitted by the LITT circumferential ablation probe is obtained by obtaining the signal output by the laser measurement sensor and generating a specific orientation of the laser emitted by the LITT circumferential ablation probe.
  • Polarity intensity wherein the LITT circumferential ablation probe is connected to a helium-neon laser with a laser wavelength of 632.8nm, and a slit diaphragm is provided between the laser measurement sensor and the LITT circumferential ablation probe, so The slit size of the slit diaphragm is 0.3mm; and the motion drive controller controls the motion driver to drive the diaphragm and the laser measurement sensor to perform circumferential and axial movements along the tapered surface of the LITT circumferential ablation probe. to obtain the spatial intensity distribution of the laser light emitted by the LITT circumferential ablation probe, wherein the aperture and the laser measurement sensor are fixedly connected to the motion driver.
  • Another aspect of this specification provides a method for preparing a fiber Bragg grating (FBG) sensor, which is characterized in that the method includes: fixing the raw material for preparing the FBG sensor to a fixing device, and the fixing device is fixedly connected to a motion driver ;
  • the laser controller controls the laser to emit laser, and the laser passes through the beam correction device, the slit diaphragm, the ultraviolet coating lens and the phase mask in sequence, and generates strip-shaped light spots on the surface of the raw material; and the motion drives the controller
  • a motion driver is controlled to drive the raw material to move. During the movement of the raw material, the raw material is irradiated by the laser, thereby forming the FBG sensor.
  • the laser is an excimer pulse laser with a characteristic wavelength of 248 nm
  • the laser generated by the laser is a rectangular flat-top beam with a central wavelength of 248 nm and a pulse duration of 15 ns.
  • the beam correction device includes two 248nm characteristic wavelength excimer laser 45° line mirrors
  • the slit diaphragm includes a 4.5mm width adjustable mechanical slit device
  • the UV-coated lens includes 245 -440nm characteristic wavelength UV-coated fused silica plano-convex cylindrical lens
  • the phase mask includes ultraviolet irradiation 248nm characteristic wavelength 1460-1600nm ultra-bandwidth phase mask
  • the strip-shaped light spot has a width of 20mm and a height of 32.4 ⁇ m.
  • MFD
  • a medical treatment device including: a magnetic resonance imaging (MRI) device configured to image a specific area including a target object to generate a magnetic resonance image; laser interstitial thermotherapy (LITT) ) device, including a LITT probe that is close to the target object and treats the target object by emitting laser light based on the magnetic resonance image; and a fiber Bragg grating (FBG) sensor configured to Obtain the temperature of the target object, wherein the FBG sensor is prepared according to the above method of preparing an FBG sensor.
  • MRI magnetic resonance imaging
  • LITT laser interstitial thermotherapy
  • FBG fiber Bragg grating
  • the FBG sensor is close to the target object and determines a temperature change of the target object, wherein the temperature change of the target object is based on the acquired thermal sensitivity S FSG of the FBG, by adjusting the Bragg wavelength drift ⁇
  • the relationship between S and temperature change ⁇ T is determined by calibration.
  • the relationship between the Bragg wavelength shift ⁇ S and the temperature change ⁇ T is obtained by placing the FBG sensor in a temperature controller, the temperature of the temperature controller changes intermittently, and at the same time, the amplified spontaneous The radiation (ASE) laser passes through the circulator and reaches the FBG sensor.
  • the reflection signal of the FBG sensor enters the telecommunications spectrum analyzer through the circulator.
  • the telecommunications spectrum analyzer monitors the reflection spectrum of the FBG sensor to determine .
  • OCT optical coherence tomography
  • the light beam deflection unit includes a needle core and a hard cladding located on the outer periphery of the needle core.
  • the beam deflection unit includes an oblique The beveled end surface is coated with a metal plating layer.
  • the first lens is a coreless lens
  • the focal length and spot size of the OCT probe are related to the length of the coreless lens and the focal length and spot size of the OCT probe.
  • the second lens is a slightly plano-convex spherical cylindrical lens
  • the starting end of the slightly plano-convex spherical cylindrical lens along the axial direction is a plane
  • the end is a sphere
  • the angle of the plane is 0° or 8°
  • the curvature of the sphere is -1.8 mm
  • the cylindrical diameter of the slightly plano-convex spherical cylindrical lens is 560 ⁇ m.
  • the beam deflection unit has a truncated axial cylinder length of 5 ⁇ m.
  • the OCT probe further includes a spring torsion coil disposed at the front end of the OCT probe; an optical sleeve housing the first lens, the second lens, the beam deflection unit and the spring torsion coil. in the optical sleeve; and a filling body filled inside the optical sleeve to fix the first lens, the second lens, and the beam deflection unit relative to the optical sleeve.
  • a medical treatment apparatus comprising: a magnetic resonance imaging (MRI) device, configured to image a specific area including a target object and generate a magnetic resonance image; a laser interstitial thermal therapy (LITT) device, comprising a LITT probe, based on the magnetic resonance image, the LITT probe approaches the target object and treats the target object by emitting laser; and an optical coherence tomography (OCT) device, configured to image the target object, the OCT device comprising the above-mentioned OCT probe.
  • MRI magnetic resonance imaging
  • LITT laser interstitial thermal therapy
  • OCT optical coherence tomography
  • the medical treatment device includes: a magnetic resonance imaging (MRI) device configured to image a specific area including a target object and generate a magnetic resonance image; a laser interstitial thermal therapy (LITT) device including a LITT probe based on the The magnetic resonance image, the LITT probe is close to the target object and treats the target object by emitting laser; and a temperature measurement element configured to obtain the temperature of a specific position on the edge of the target object, the The specific position is the farthest position from the LITT probe on the edge of the target object.
  • MRI magnetic resonance imaging
  • LITT laser interstitial thermal therapy
  • the temperature measurement element includes a LITT photon temperature measurement probe.
  • the medical treatment device further includes a processing module configured to, when the temperature measured by the temperature measuring element exceeds the preset temperature range, based on the measured temperature and the preset temperature range. The difference between the temperature ranges determines the target laser output dose value of the LITT device so that the temperature measured by the temperature measuring element is within the preset temperature range.
  • the medical treatment device further includes a laser power attenuator configured to adjust the current laser output dose value to the target laser output dose value.
  • the laser power attenuator dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measuring element is always within the preset temperature range.
  • the preset temperature range is 46 ⁇ 1°C.
  • the LITT probe is a LITT lateral ablation probe or a LITT circumferential ablation probe.
  • the LITT circumferential ablation probe is disposed at the equivalent center of the target object, and the temperature measurement element is disposed on the edge of the target object farthest from the LITT circumferential ablation probe.
  • the distance between the LITT circumferential ablation probe and the temperature measuring element is equal to or close to the equivalent radius of the target object.
  • the LITT lateral ablation probe is disposed on one edge of the target object, and the temperature measurement element is disposed on the edge of the opposite side of the target object at a distance from the LITT lateral ablation probe. At the farthest position of the probe, the distance between the LITT lateral ablation probe and the temperature measurement element is equal to or close to the equivalent diameter of the target object.
  • the medical treatment apparatus further comprises an optical coherence tomography (OCT) device configured to image the target object and generate an OCT image.
  • OCT optical coherence tomography
  • the OCT device includes an OCT probe that emits a light signal to the target object to image the target object during treatment, and the OCT probe emits a light signal.
  • the optical signal has two different central wavelengths.
  • the medical treatment device further includes a first driving device coupled to the LITT probe and controlling the translational movement and rotational movement of the LITT probe; and a second driving device coupled to the LITT probe. temperature measuring element, and control the translational movement of the temperature measuring element.
  • the first driving device includes a first translation cable and a first rotation cable, and a first translation control mechanism and a first rotation control mechanism, wherein the first translation cable and the first rotation control mechanism
  • the rotation cables are respectively connected to the first translation control mechanism and the first rotation control mechanism.
  • the first translation control mechanism and the first rotation control mechanism are connected to the LITT probe. Through the first translation cable and The first rotation cable controls the translational movement and rotational movement of the LITT probe respectively.
  • the second driving device includes a second translation cable; and a second translation control mechanism, wherein the second translation cable is connected to the second translation control mechanism, and the second translation A control mechanism is connected to the temperature measuring element and controls the translational movement of the temperature measuring element through the second translation cable.
  • Figure 1 is a medical treatment system according to some embodiments of the present specification.
  • 2A-2D are exemplary structural diagrams of medical treatment devices according to some embodiments of the present specification.
  • 3A and 3B are structural schematic diagrams of an exemplary driving device according to some embodiments of this specification.
  • 4A-4C are structural schematic diagrams of exemplary translation control mechanisms and/or rotation control mechanisms according to some embodiments of this specification.
  • FIG. 5 is an exemplary structural diagram of a control device according to some embodiments of this specification.
  • FIG. 6 is an illustration of two different types of integrated probes in accordance with some embodiments of the present specification.
  • Figure 7 shows an exemplary LITT lateral ablation probe prepared by the first process according to some embodiments of the present specification.
  • Figure 8 shows an exemplary LITT lateral ablation core prepared by the second process according to some embodiments of the present specification.
  • Figure 9 illustrates an exemplary LITT circumferential ablation probe in accordance with some embodiments of the present specification.
  • Figure 10 is a schematic diagram of an exemplary tapered surface processing according to some embodiments of the present specification.
  • FIG. 11 is a schematic diagram of processing of exemplary cross-threaded grooves according to some embodiments of the present specification.
  • Figure 12 is a schematic diagram of vector light energy distribution of a LITT circumferential ablation probe tested according to some embodiments of this specification.
  • Figure 13 is a schematic diagram of temperature measurement using a thermocouple according to some embodiments of this specification.
  • Figure 14 is a schematic diagram of temperature measurement using an FBG sensor according to some embodiments of this specification.
  • Figure 15 is an exemplary OCT probe according to some embodiments of the present specification.
  • Figure 16 is a schematic diagram of preparing an FBG sensor according to some embodiments of this specification.
  • Figure 17 is a schematic diagram of a medical treatment device according to other embodiments of this specification.
  • Figure 18 is a schematic diagram of a LITT photon temperature measurement probe according to some embodiments of the present specification.
  • Figure 19 is a schematic diagram of a LITT photon ablation probe according to some embodiments of the present specification.
  • FIG. 20 is a schematic diagram of a LITT photon ablation probe and a LITT photon temperature measurement probe during treatment according to some embodiments of the present specification.
  • FIG. 1 is a diagram showing a medical treatment system according to some embodiments of the present specification.
  • the medical treatment system 100 is used for medical diagnosis and/or treatment of target objects.
  • the target object may include biological objects (such as human body, animals, etc.).
  • the target object may include the human body or specific parts thereof, such as the head, and/or tissues to be treated, lesions (such as brain tumors and epileptic lesions), etc., or combinations thereof.
  • MRg-LITT magnetic resonance guided laser interstitial thermal therapy
  • MRI magnetic resonance imaging
  • the medical treatment system 100 is not limited to MRg-LITT, and may also be other types of treatment systems, such as MRg microwave treatment, etc.
  • the medical treatment system 100 includes an MRI device 110, a LITT device 120, a temperature measurement element 130, a control device 140, a terminal 150, and an optical coherence tomography (OCT) device (not shown in the figure). ).
  • OCT optical coherence tomography
  • the MRI device 110 is configured to scan a specific area containing a target object and generate an MRI image.
  • the MRI device 110 may be an MRI scanner.
  • the MRI scanner includes a magnet module and a radio frequency (RF) module.
  • the magnet module may include a main magnetic field generator and/or a gradient magnetic field generator.
  • the main magnetic field generator may include a main magnet that generates a static magnetic field B0 during an MRI scan.
  • the main magnet may be a permanent magnet, a superconducting electromagnet, a resistive electromagnet, etc.
  • the gradient magnetic field generator may generate a magnetic field gradient in the X, Y and/or Z directions.
  • the X direction may also be referred to as a readout (RO) direction
  • the Y direction may also be referred to as a phase encoding (PE) direction
  • the Z direction may also be referred to as a slice selection (SS) direction.
  • the gradient magnetic field may encode spatial information of the target object.
  • the RF module may include an RF transmitting coil and/or a receiving coil.
  • the RF transmitting coil may transmit an RF signal (or radio frequency pulse) to excite a region of interest and generate an MRI signal.
  • the RF receiving coil may receive an echo signal emitted by the region of interest.
  • the RF signal may be a 30° pulse signal, a 40° pulse signal, a 60° pulse signal, etc.
  • the MRI device 110 may process the MRI signals to generate an MRI image, which may represent anatomical structure information of a specific region of the target object.
  • the functionality, size, type, geometry, location, and number of magnet modules and/or RF modules may be determined or changed based on one or more specific conditions.
  • RF coils can be divided into body coils and local coils based on differences in function and size.
  • the body coil may be configured as a birdcage coil, a transverse electromagnetic coil, a saddle coil, or the like.
  • the local coils may include phased array coils, loop coils, etc.
  • the local coils may include Holmhertz head coils.
  • the Holmhertz head coil can create a small-scale uniform magnetic field in the patient's head area, send RF signals and receive corresponding head MRI signals.
  • the head MRI signal can be used to image the patient's head to generate a head MRI image.
  • the MRI device 110 can also acquire thermal image data from the MRI scanner for magnetic resonance thermography (MRTI). Based on the thermal image data, a thermal image is reconstructed.
  • the thermal image may represent temperature changes in a specific area containing the target object.
  • each pixel/voxel in the thermal image can measure the temperature change at the corresponding location within the specific area.
  • the LITT device 120 is configured to generate laser light and utilize the thermal effect of the laser light to treat, eg, ablate, the target object. Based on the above-mentioned MRI images and/or thermal images, the location and size of the target object (eg, tumor) can be determined, thereby effectively and controllably guiding the LITT device 120 to emit laser light to perform thermal therapy on the target object.
  • the target object eg, tumor
  • the LITT device 120 includes a laser, a LITT probe, and a channel (such as an optical fiber) and an interface connecting the laser and the LITT probe.
  • the laser can be used to emit laser light.
  • the laser can be a solid laser, a gas laser, a liquid laser, a semiconductor laser, a free electron laser, etc.
  • the wavelength of the laser generated by the laser is within a certain range, for example, the near-infrared region (0.75-2.5 microns ( ⁇ m)).
  • the laser emitted by the laser is transmitted to the LITT probe through the optical fiber and the interface.
  • LITT probe also called LITT probe or LITT diffusion applicator
  • LITT probe is used as a treatment probe to deliver the laser light generated by the laser to the target object to achieve ablation treatment of lesions.
  • the LITT probe includes the probe body.
  • the probe body can be configured in different structures. Under different structures, the position of laser emission is different. Specifically, according to the difference in the exit position, the LITT probe can be divided into a LITT lateral ablation probe and a LITT circumferential ablation probe.
  • a LITT lateral ablation probe refers to a LITT probe in which the laser emission position is located at the end (distal end) of the probe. At this time, the laser emission direction is the same as or at a certain angle with the axial direction of the LITT probe.
  • LITT circumferential ablation probe refers to a LITT probe in which the laser emission position is evenly distributed in the circumference of the probe. At this time, the laser emission direction is the radial direction of the LITT probe, and is evenly dispersed around the circumference of the LITT probe.
  • the type, specific structure and process of the LITT probe reference can be made to other drawings (for example, Figures 6-11) and their descriptions in this application, which will not be described again here.
  • the temperature measurement element 130 is used to measure the temperature of the target object or its surrounding tissue and/or the LITT probe.
  • the temperature measuring element 130 can be close to the target object and obtain the temperature of the target object and its surrounding tissues.
  • the LITT device 120 can transfer heat to the target object through the LITT probe in a controlled manner to treat the target object and protect the healthy tissue surrounding the target object.
  • the temperature measurement element 130 may include a thermocouple, a fiber Bragg grating (FBG) sensor, or the like.
  • Thermocouples can directly measure temperature and convert the temperature signal into a thermoelectromotive force signal. The thermoelectromotive force signal can be further converted into the temperature of the object being measured.
  • Thermocouples can include K-type thermocouples, T-type thermocouples, E-type thermocouples, S-type thermocouples, B-type thermocouples, etc.
  • the thermocouple is a K-type thermocouple.
  • the FBG sensor is a sensor in which a specific position of the optical fiber is made into a grating with a periodic distribution of refractive index, and the grating area is used as the sensing area. Light waves of specific wavelengths (Bragg reflected light) are reflected in this grating area.
  • the reflected center wavelength signal is related to the grating period and the effective refractive index of the fiber core.
  • the control device 140 is used to control one or more components of the medical treatment system 100 and perform corresponding operations.
  • the control device 140 can generate corresponding instructions based on the components being controlled and the operations that need to be performed.
  • the instructions are conveyed to the controlled component in the form of electrical signals, causing the component to perform corresponding operations.
  • the control device 140 may receive request or command information input through the terminal 150, and the MRI device 110 and/or the temperature measurement element 130 may generate information (eg, images, temperature data, etc.). Based on the above information, the control device 140 may generate control instructions.
  • the control instructions may be sent to the LITT device 120 for treating the target subject.
  • control device 140 may be a microcontroller unit (MCU), a central processing unit (CPU), a programmable logic device (PLD), an application specific integrated circuit (ASIC), a single chip microcomputer (SCM), a system on chip (SoC), etc.
  • MCU microcontroller unit
  • CPU central processing unit
  • PLD programmable logic device
  • ASIC application specific integrated circuit
  • SCM single chip microcomputer
  • SoC system on chip
  • the terminal 150 may be used for input/output of information (eg, images, data, etc.).
  • the terminal 150 may include a computer, a mobile device (eg, a mobile phone, a tablet, a laptop), etc., or any combination thereof.
  • the terminal 150 may include a wearable device, a virtual reality device, an augmented reality device, etc., or any combination thereof.
  • Wearable devices include bracelets, glasses, helmets, watches, etc., or any combination thereof.
  • Virtual reality devices and/or augmented reality devices include virtual reality helmets, virtual reality glasses, virtual reality goggles, augmented reality helmets, augmented reality glasses, augmented reality goggles, etc., or any combination thereof.
  • virtual reality devices and/or augmented reality devices may include Google Glass TM , Oculus Rift TM , Hololens TM , Gear VR TM , etc.
  • terminal 150 may be part of control device 140.
  • the OCT device uses low-coherence interference of a broadband light source to image the target object and generate high-resolution (e.g., micrometer-level) and/or ultra-depth OCT images.
  • the OCT device includes a time-domain optical coherence tomography (TDOCT) device, a spectral domain optical coherence tomography (SDOCT) device, and/or a swept-frequency optical coherence tomography (SSOCT) device.
  • TDOCT time-domain optical coherence tomography
  • SDOCT spectral domain optical coherence tomography
  • SSOCT swept-frequency optical coherence tomography
  • the OCT device includes a light source, an OCT probe, an interference component, and optical fibers and interfaces connecting each component.
  • the light source uses a low-coherence light source to improve the longitudinal resolution of imaging.
  • the OCT probe is used to emit light emitted by the light source to a target object and receive light reflected by the light source.
  • the low-coherence light emitted by the light source can be divided into reference light and sample light (emitted by the OCT probe). Each interferes through the interference component after being reflected by the reference mirror and reflected (or retroreflected) by the tissue of the target object. Based on the interference spectrum formed by the interference, the OCT device (for example, the optoelectronic system therein) can obtain depth information of the structure of the target object.
  • an OCT image of the target object can be generated.
  • the OCT image is a two-dimensional or three-dimensional image.
  • the OCT device can provide pathological imaging. Combined with the LITT device, it can detect the cancerous pathological residue of the ablation lesion in real time, and perform rapid supplementary ablation on the remaining cancerous pathological imaging of the ablation lesion margin, so that the canceration residue and recurrence can be eliminated. The possibility is reduced to a minimum.
  • Each device or component of the medical treatment system 100 may be a local device or component or a remote device or component. Each device or component is connected in one or more various ways.
  • the control device 140 may be a remote device, and the LITT device 110 and the MRI device 120 may be connected to the control device 140 through a network.
  • the control device 140 may be a local device, and the LITT device 110 and the MRI device 120 may be directly connected to the control device 140 .
  • terminal 150 may be connected to control device 140 directly or through a network.
  • the network may include any suitable network that facilitates the exchange of information and/or data with the medical treatment system 100 .
  • the network may be and/or include a public network (eg, the Internet), a private network (eg, a local area network (LAN), a wide area network (WAN)), a wired network (eg, an Ethernet network), a wireless network (eg, an Ethernet network) (e.g., 802.11 networks, Wi-Fi networks), cellular networks (e.g., Long Term Evolution (LTE) networks), Frame Relay networks, virtual private networks (“VPNs”), satellite networks, telephone networks, routers, hubs, switches, servers Computer and/or any combination thereof.
  • a public network eg, the Internet
  • a private network eg, a local area network (LAN), a wide area network (WAN)
  • a wired network eg, an Ethernet network
  • a wireless network e.g., an Ethernet network
  • cellular networks e.g., Long Term Evolution (LTE) networks
  • Frame Relay networks e.g., virtual private networks (“VPNs”), satellite networks, telephone networks
  • the network may include a cable network, a wired network, a fiber optic network, a telecommunications network, an intranet, a wireless local area network (WLAN), a metropolitan area network (MAN), a public switched telephone network (PSTN), a BluetoothTM network , ZifengTM network, near field communication (NFC) network, etc., or any combination thereof.
  • WLAN wireless local area network
  • MAN metropolitan area network
  • PSTN public switched telephone network
  • BluetoothTM network ZifengTM network
  • NFC near field communication
  • 2A-2D are exemplary structural diagrams of medical treatment devices according to some embodiments of the present specification.
  • the medical treatment device 200 may be a device that integrates various devices and components in the medical treatment system 100 (local or remote). As shown in the figure, the medical treatment device 200 may include a support fixed platform 201, an MRI device 202, a head coil 203, a LITT device (not shown in the figure), an OCT device (not shown in the figure), and a temperature measurement element (Fig. (not shown in the figure), cooling equipment (not shown in the figure), driving device 204, interface platform 205, control relay platform 206, integrated component 207, control device 208, and terminal 209.
  • a support fixed platform 201 an MRI device 202, a head coil 203, a LITT device (not shown in the figure), an OCT device (not shown in the figure), and a temperature measurement element (Fig. (not shown in the figure), cooling equipment (not shown in the figure), driving device 204, interface platform 205, control relay platform 206, integrated component 207, control device 208, and terminal 209.
  • the support and fixation platform 201 also called a treatment bed, is used to support and/or fix the patient to prevent displacement of the patient or its specific parts during treatment.
  • the support and fixed platform 201 can move (eg, translate, tilt, rotate, etc.) based on control instructions issued by the control device 208 to adjust the patient's posture layout during medical diagnosis and/or treatment.
  • the support fixed platform 201 can translate or tilt based on the control instructions issued by the control device 208 during the MRI scanning and imaging process to provide a better scanning position reference for the MRI.
  • the MRI device 202 is used to image a specific area including a target object (e.g., a tumor in the patient's brain) to generate an MRI image.
  • the MRI image may be a real-time MRI image or a non-real-time MRI image.
  • the MRI image may include a three-dimensional image or multiple two-dimensional images (e.g., cross-sectional, coronal, and sagittal images) to characterize information about the target object in three-dimensional space (e.g., position and size, etc.).
  • the information about the target object in three-dimensional space provided by the MRI image can be used to plan the path for the LITT probe, OCT probe, and/or temperature measuring element to pass through human tissue to reach the target object before treatment (referred to as needle insertion planning).
  • the information about the target object in three-dimensional space provided by the MRI image can also be used to guide the LITT probe, OCT probe, and/or temperature measuring element to enter human tissue along the planned path and reach the target object during treatment (referred to as needle insertion guidance).
  • the MRI image may be displayed on the terminal 209.
  • a user such as a doctor, can perform needle insertion planning and needle insertion guidance of the LITT probe based on the MRI image through the terminal 209 (e.g., physical elements such as a touch screen, mouse, and keyboard on the terminal 209).
  • the system may also automatically perform needle insertion planning and guidance of the LITT probe based on the MRI image.
  • the MRI device 202 can also perform magnetic resonance thermography on a specific area including the target object to generate a thermal image.
  • the thermal image can be registered with the MRI image, and simultaneously represents the anatomical structure information of the specific area containing the target object and the temperature change information of the corresponding location.
  • the head coil 203 is used to provide deeper head MRI signals.
  • head coil 203 is a Holmhertz magnetic coil.
  • the target object eg, a tumor
  • the head coil 203 can transmit RF signals and receive head MRI signals.
  • the head MRI signal collected by the head coil 203 has a higher signal-to-noise ratio (SNR) than the MRI signal collected by the MRI device 202 .
  • SNR signal-to-noise ratio
  • the head coil 203 may be coupled to the MRI device 202 through an interface to generate more accurate head MRI images.
  • head coil 203 can acquire head thermal image data for head MRTI. Based on the head thermal image data, a thermal image of the patient's head can be reconstructed. In some embodiments, the head coil 203 can also support and fixate the patient's head.
  • the LITT equipment is used to generate laser light and use the thermal effect of the laser to treat the target object.
  • the LITT device includes a laser, a LITT probe (eg, a LITT lateral ablation probe, a LITT circumferential ablation probe), and a channel (such as an optical fiber) and interface connecting the laser and the LITT probe.
  • the laser may include a tunable laser diode and/or a non-tunable laser diode.
  • the laser power of the tunable laser diode is tunable within a specific range, for example, 0W-500W, 10-250W, 50-150W, etc.
  • the laser power of the non-tunable laser diode is a specific value, for example, 10W, 12W, 15W, 20W, 30W, 60W, 100W, 150W, etc.
  • the LITT device includes a LITT probe displacement controller 210 for controlling the displacement of the LITT probe.
  • the LITT probe displacement controller 210 controls the LITT probe to pass through the needle insertion channel fixedly provided on the interface platform 206, pass through the patient's skull, enter the skull, and reach the target according to the needle insertion planning and needle insertion guidance. The location of the target object.
  • the interface platform 206 is fixed to the patient's head.
  • the medical treatment device 200 may include a displacement sensor (not shown in the figure) for real-time feedback of displacement data of the LITT probe during the needle insertion process.
  • the displacement sensor may be, for example, a piezoelectric sensor, an inductive sensor, an eddy current sensor, etc.
  • the displacement sensor may be connected to the LITT probe.
  • the displacement sensor may be disposed on the interface platform 206 .
  • the laser light emitted by the laser is processed by the optical path relay processing device 211 and then transmitted to the LITT probe.
  • the optical path relay processing device 211 can adjust the parameters of the laser (for example, power, frequency, etc.). For example, the optical path relay processing device 211 can compensate for the attenuation of the laser so that it reaches a specific power, or perform attenuation processing on the laser so that its power meets the needs of treatment.
  • the optical path relay processing device 211 is provided on the control relay platform 204 .
  • the OCT device Based on the light transmittance of biological structures, the OCT device detects the reflection, scattering and other signals of biological tissues, converts them into electrical signals, and generates OCT images.
  • the OCT image is a real-time OCT image, and can also be a non-real-time OCT image.
  • the OCT device includes a light source, an OCT probe, an interference component, and optical fibers and interfaces connecting the components.
  • the light source uses a low-coherence light source to improve the longitudinal resolution of imaging.
  • the exemplary structure of the OCT probe can refer to other drawings (e.g., Figure 15) and their descriptions in this application, and will not be repeated here.
  • the OCT device may be a dual-mode OCT, and its light source may generate optical signals with two different parameters (bandwidth, central wavelength).
  • the dual-mode OCT uses an optical signal with a central wavelength of 840 nm over a 160 nm bandwidth, and a central wavelength of 1300 nm over a 100 nm sweep range.
  • Dual-mode OCT can provide pathological imaging with a resolution close to 1 ⁇ m and a depth of cm.
  • the optical fiber slip ring device 212 can be used to ensure uninterrupted transmission of the optical signal.
  • a multi-channel optical fiber slip ring device can be used (such as a dual-channel optical fiber slip ring device to adapt to the above-mentioned two optical signals with different central wavelengths), also called a multi-mode optical fiber slip ring device.
  • the optical fiber slip ring device 212 may be disposed on the control relay platform 204 .
  • the temperature measuring element is used to measure the temperature of the target object or its surrounding tissue and/or the LITT probe.
  • Temperature measuring elements can include thermocouples (such as K-type thermocouples), FBG sensors, etc.
  • the FBG sensor is prepared using specially prepared raw materials.
  • the raw material must meet certain parameters.
  • the above-mentioned raw materials are irradiated with ultraviolet light in a specific wavelength range (for example, 240-244nm, 244-248nm, 248-252nm, 252-256nm, etc.), so that the refractive index of the optical fiber core is periodically modulated.
  • Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other.
  • the input beam only experiences strong reflection at specific wavelengths determined by certain phase matching conditions.
  • the reflected wavelength is called the Bragg wavelength of the FBG.
  • the phase matching condition called the Bragg condition, ultimately forms the FBG sensor.
  • the FBG sensor can be used for real-time monitoring of interstitial tissue (eg, target object and its surrounding tissue) and LITT probe (distal) temperature during diffuse laser ablation irradiation.
  • interstitial tissue eg, target object and its surrounding tissue
  • LITT probe distal temperature during diffuse laser ablation irradiation.
  • Cooling equipment is used to control the temperature of the LITT probe. Since the LITT probe emits laser light and uses the thermal effect of the laser to treat the target object, the temperature of the LITT probe will increase as the treatment time increases during the treatment process. Excessive temperature will not only affect the normal operation of the probe, but also damage normal human tissues and may cause postoperative sequelae.
  • the cooling device delivers a specific cooling medium (for example, CO 2 gas) to the distal end of the LITT probe through the cooling channel 214 to cool down the LITT probe.
  • the cooling device includes a cooling source (not shown), a cooling control element 213 and a cooling channel 214 .
  • the cooling source is used to store the cooling medium.
  • the cooling medium may be CO2 gas.
  • the cooling source may be a CO2 gas source tank for storing CO2 gas.
  • the cooling control element 213 can control the on and off of the cooling source, as well as the parameters of the cooling medium (for example, the flow rate and pressure of CO 2 gas), etc.
  • the above-mentioned LITT probe, OCT probe, temperature measurement element and/or cooling channel can be integrated into one body to form an integrated probe 224 that integrates diagnosis and treatment (hereinafter referred to as integrated probe 224).
  • the temperature measuring element and the LITT probe can be integrated into one body to form the integrated probe 224 .
  • the above-mentioned OCT probe can be integrated with the temperature measurement element and the LITT probe to form an integrated probe 224 .
  • the above-mentioned LITT probe, OCT probe, temperature measurement element and cooling channel can be integrated into one body to form the integrated probe 224 .
  • the drive device 204 is used to drive the LITT probe (e.g., the integrated probe 224) to move to reach the location of the target object (needle insertion) or away from the location of the target object (withdrawal).
  • the movement may include linear translation and rotation.
  • the drive device 204 includes a drive motor, a cable, and a motion control mechanism.
  • the LITT probe is physically connected to the motion control mechanism.
  • the force output by the drive motor can be transmitted to the integrated probe 224 to control its movement.
  • the cable includes a translation cable 215 and a rotation cable 216.
  • the motion control mechanism includes a translation control mechanism 217 and a rotation control mechanism 218.
  • the translation control mechanism 217 is used to control the translation movement of the integrated probe 224.
  • the rotation control mechanism 218 is used to control the rotation movement of the integrated probe 224.
  • the translation cable 215 and the rotation cable 216 are connected to the translation control mechanism 217 and the rotation control mechanism 218, respectively.
  • the cables (such as the translation cable 215 and the rotation cable 216) are specific silk threads with high rigidity and low elastic modulus, and can complete torque transmission in real time 1:1 to ensure the accuracy of driving the LITT probe movement.
  • the drive motor can drive the translation cable 215 and/or the rotation cable 216 to move as required, and control the translation and/or rotation of the integrated probe 224 via the translation control mechanism 217 and/or the rotation control mechanism 218. Movement to achieve precise motion control of the two degrees of freedom of the LITT probe (or integrated probe 224).
  • the translation control mechanism 217 and the rotation control mechanism 218 may be provided on the interface platform 205 .
  • Interface platform 205 may carry one or more components or elements of medical treatment device 200 .
  • the mounted components or elements include the needle entry channel of the LITT probe, a displacement sensor, a motion control mechanism (such as a translation control mechanism 217 and a rotation control mechanism 218), etc.
  • interface platform 205 may be a biaxial stereoscopic frame, as shown in the figure.
  • the interface platform 205 can be fixed to the patient's head (skull) and maintain a stable connection with the patient's head without relative displacement.
  • the components or elements carried by the interface platform 205 can be fixedly connected to the biaxial three-dimensional frame.
  • the LITT probe (the above-mentioned integrated probe 224) can enter the patient's skull through the needle insertion channel provided by the interface platform 205 through the needle insertion path, and accurately reach the location of the target object.
  • Control relay platform 206 integrates mid-stage or relay control of one or more components or elements of medical treatment device 200 .
  • the control relay platform 206 integrates the above-mentioned LITT probe displacement controller 210, optical path relay processing device 211, OCT optical fiber slip ring 212, cooling control element 213, and some components of the driving device 204, such as a driving motor.
  • a packaging box is provided on the control relay platform 206.
  • the LITT probe displacement controller 210, the optical path relay processing device 211, the OCT optical fiber slip ring 212, and the cooling control element 213 are arranged in the packaging box.
  • 5 channels are introduced in the packaging box, including OCT probe channel 219 (optical fiber), LITT probe channel 220 (optical fiber), cooling channel 214, temperature measurement element control cable channel 221 and displacement sensor cable Channel 222.
  • OCT optical fiber slip ring 212 is connected to the OCT probe channel 219;
  • the optical path relay processing device 211 is connected to the LITT probe channel 220 and the temperature measurement element control cable channel 221;
  • the cooling control element 213 is connected to the cooling channel 214;
  • the connector 210 is connected to the displacement sensor cable channel 222.
  • the integrated component 207 is used to integrate signal control cables, optical channels, cooling channels, etc. of the medical treatment device 200 .
  • the integrated component 207 can integrate the OCT probe channel 219, the LITT probe channel 220, the cooling channel 214 and the temperature measurement element control cable channel 221, etc., for example, mechanical coupling .
  • the integrated component 207 includes an integrated pipeline 223 that can accommodate an OCT probe channel 219, a LITT probe channel 220, a cooling channel 214, and a temperature measuring element control cable channel 221.
  • the integrated pipeline 223 may be connected to the integrated probe 224 , for example, sealingly connected to the housing of the integrated probe 224 .
  • the control device 208 may be used to control one or more components of the medical treatment device 200 and perform corresponding operations.
  • the control device 208 can generate corresponding instructions based on the components being controlled and the operations that need to be performed.
  • the instructions are conveyed to the corresponding component in the form of electrical signals, causing the component to perform corresponding operations.
  • the control device 208 integrates an OCT imaging control module, a LITT treatment control module, a temperature measurement element temperature control module, a head coil imaging registration module, a cooling system control module, and a LITT probe position sensing control module.
  • the terminal 209 can display information related to each component in the medical treatment device 200 and the patient in the form of images, data, etc.
  • the terminal 209 can display the MRI image of the target object, the thermal image, the registration image of the MRI image and the thermal image, the OCT image, the temperature information measured by the temperature measurement element, and the cooling information of the LITT probe by the cooling device.
  • terminal 209 may also receive user-entered information.
  • Information input through the terminal 209 may include images, numbers, text, voice, etc.
  • the user can input one or more operation instructions through the terminal 209.
  • the operation instructions may include instructions for adjusting the patient's body position layout, operating mode/parameter setting instructions for the MRI equipment 202, head coil 203, LITT equipment (such as LITT probe), OCT equipment (such as OCT probe), cooling equipment, etc. , LITT probe needle path planning instructions during treatment, etc.
  • Information entered via terminal 209 may be sent to control device 208 .
  • the control device 208 can generate control instructions to control the corresponding device or component to perform corresponding operations.
  • the terminal 209 may be or include a computer, a mobile phone, a tablet, a console, etc.
  • MRI compatible refers to the component's ability to be used in an MRI environment.
  • the operation of MRI-compatible components will not cause significant interference to MRI.
  • specific environments for example, 0.5T, 0.75T, 1T, 1.5T, 2.0T, 3.0T, etc.
  • the above There is no danger in the operation of the components.
  • 3A and 3B are structural schematic diagrams of an exemplary driving device according to some embodiments of this specification.
  • the driving device 300 includes a power input terminal 301 , cables 302 and 303 , and a power output terminal 304 .
  • the power output 304 is connected to the LITT probe (or integrated probe 224).
  • the power input from the power input terminal 301 can be transmitted to the power output terminal 304 to drive the LITT probe (or integrated probe 224) to move.
  • the power output end 301 may be a driving motor.
  • Cables 302 and 303 are respectively translation cables and rotation cables, respectively controlling the translation movement and rotation movement of the LITT probe (or integrated probe 224).
  • the driving device 300 additionally includes driving knobs 305 and 306 .
  • the drive knob 305 and the cable 303 are connected through two meshed bevel gears 307 and 308.
  • Two meshed bevel gears 307 and 308 constitute a bevel gear transmission mechanism. Therefore, by rotating the drive knob 305, the cable 303 can also be driven to move, thereby controlling the movement (for example, rotational movement) of the LITT probe (or integrated probe 224). .
  • the torque can be increased and transmitted, so that a smaller driving torque on the driving knob 305 can drive the movement of the cable 303.
  • the drive knob 306 and the cable 302 are also connected through two meshing bevel gears.
  • the driving knobs 305 and 306 can be manually controlled to drive the movement of the cables 303 and 302 respectively, thereby controlling the movement of the LITT probe (or integrated probe 224) as a supplement to the motor driving method, and at the same time, Have better flexibility.
  • 4A-4C are structural schematic diagrams of exemplary translation control mechanisms and/or rotation control mechanisms according to some embodiments of this specification.
  • the figure shows the power output end 304 at different viewing angles.
  • the power output end 304 includes a translation control mechanism and a rotation control mechanism.
  • the translation control mechanism and the rotation control mechanism directly control the translation movement and rotation movement of the LITT probe (or integrated probe 224) respectively.
  • the rotation control mechanism includes a set of timing belt drive assemblies 403 .
  • the timing belt drive assembly 403 connects the LITT probe channel 404 and the rotation cable.
  • the LITT probe (or integrated probe 224) is fixedly disposed in the LITT probe channel 404.
  • the displacement of the rotating cable is converted by the intermediate element (for example, bevel gear combination, worm gear combination), driving the synchronous belt transmission assembly 403 to rotate, thereby causing the LITT probe (or integrated probe 224 ) to rotate.
  • This synchronous belt transmission assembly 403 completes motion control of the LITT probe (or integrated probe 224) at a certain rotation speed through a specific reduction ratio.
  • the translation control mechanism includes a worm gear assembly 401 and a synchronous belt transmission assembly 402. As shown in Figures 4B and 4C, the displacement of the translation cable changes the input shaft orientation through the worm gear assembly 401 and is transmitted to the synchronous belt transmission assembly 402 to realize translation of the LITT probe (or integrated probe 224). At the same time, a certain self-locking effect can also be achieved to make the LITT probe (or integrated probe 224) more stable and free from external force interference.
  • the translation control mechanism and the rotation control mechanism can also be implemented through a gear set transmission mechanism.
  • FIG. 5 is an exemplary structural diagram of a control device according to some embodiments of this specification.
  • control device 208 includes an OCT imaging control module 501, a LITT treatment control module 502, a temperature measurement element temperature control module 503, a head coil imaging registration module 504, a cooling system control module 505, and a LITT probe position sensing module.
  • the OCT imaging control module 501 is used to control OCT imaging.
  • the OCT imaging control module 501 can control the OCT device to emit optical signals and set imaging parameters (for example, optical signal bandwidth, central wavelength of the optical signal, imaging time, image contrast, etc.) by generating instructions.
  • the OCT imaging control module 501 can also acquire the generated pathological diagnosis signal to generate an OCT image.
  • the optical signal emitted by the OCT equipment is transmitted to the OCT probe through the optical fiber slip ring device 212.
  • the LITT treatment control module 502 is used to control the LITT probe to treat the target object.
  • LITT treatment control module 502 integrates a laser controller, a tunable laser diode and/or a non-tunable laser diode.
  • the laser controller can control the laser (eg, the tunable laser diode and/or the non-tunable laser diode) to emit laser light to provide an ablation energy source for the entire LITT.
  • the LITT treatment control module 502 can control the laser to emit laser, and the emitted laser is transmitted to the LITT probe through the optical path relay processing device 211.
  • the temperature measurement element temperature control module 503 is used to control the temperature measurement element to measure the temperature of the target object and its surrounding tissues and/or the LITT probe.
  • the temperature measurement signal of the temperature measurement element (such as the FBG sensor heat source optical signal or the K-type thermocouple analog temperature control signal) can be transmitted through the optical path relay processing device 211.
  • the head coil imaging registration module 504 is used to control the registration of the imaging of the head coil (such as head MRI image, head thermal image) and the imaging of the MRI equipment (such as MRI image, thermal image), so as to obtain clearer, Images that are accurate and provide temperature information.
  • the imaging of the head coil such as head MRI image, head thermal image
  • the imaging of the MRI equipment such as MRI image, thermal image
  • the cooling system control module 505 is used to control the cooling equipment to cool the LITT probe.
  • the cooling system control module 505 can control the opening and closing of the cooling source and the parameters of the cooling medium (for example, the flow rate and pressure of CO 2 gas) through the cooling control element 213, combined with the temperature of the LITT probe measured by the temperature measuring element. , controls the temperature of the LITT probe to prevent the probe from overheating and damage, and plays a role in protecting the probe.
  • the temperature of the target object and its surrounding tissue measured by the temperature measuring element can also be combined to control the temperature of the healthy tissue surrounding the target object to avoid unnecessary damage.
  • the cooling system control module 505 can control the cooling medium to be recycled through the cooling channel.
  • the LITT probe position sensing control module 506 is used to detect the real-time position of the LITT probe deep into the skull in real time by controlling the LITT probe displacement controller 210 .
  • the LITT probe position sensing control module 506 can also send control signals to the LITT probe displacement controller 210 in real time, issue displacement triggering instructions and receive position feedback processing signals.
  • the displacement triggering instruction is used to trigger the LITT probe displacement controller 210 to control the movement of the LITT probe.
  • the position feedback processing signal is used to judge and decide the subsequent movement of the LITT probe (for example, continue to move forward, adjust direction, retreat, etc.) based on the real-time position of the LITT probe.
  • the drive control module 507 is used to control the drive motor of the drive device 204 to drive the translation cable 215 and/or the rotation cable 216, and control the LITT probe ( Or the translational and/or rotational movement of the integrated probe 224), achieving precise motion control of the two degrees of freedom of the LITT probe (or the integrated probe 224).
  • the support and fixed platform control module 508 is used to control the movement of the support and fixed platform 201 .
  • the support and fixed platform control module 508 controls the movement of the support and fixed platform 201 (for example, translation, tilt, rotation, etc.) by issuing motion control instructions to adjust the patient's posture layout and provide a better scanning position reference for MRI.
  • FIG. 6 is an illustration of two different types of integrated probes in accordance with some embodiments of the present specification.
  • the integrated probe 224 is connected to an OCT probe channel, a LITT probe channel, a cooling channel and a temperature measurement element control cable channel.
  • the above four channels are mechanically coupled through the integrated component 207 and are jointly accommodated in the integrated pipeline of the integrated component 207 .
  • the integrated pipeline is connected to the integrated probe 224 directly or through an interface.
  • the integrated pipeline is connected to the integrated probe 224 through the interface 601 .
  • the interface 601 is provided on the interface platform 205.
  • the two different types of integrated probes may include a LITT lateral ablation integrated probe 610 and a LITT circumferential ablation integrated probe 660.
  • the LITT lateral ablation integrated probe 610 includes a temperature measuring element 611, a CO2 gas supply tube 612, a LITT lateral ablation probe 613 (also called a LITT lateral ablation needle core), an OCT probe 614, and a CO2 gas collection tube 615.
  • the LITT lateral ablation probe 613 in the LITT lateral ablation integrated probe 610 can be prepared by at least two different processes.
  • the LITT circumferential ablation integrated probe 660 includes a temperature measurement element 661, a CO 2 air supply tube 662, a LITT circumferential ablation probe 663 (also called a LITT circumferential ablation needle core), an OCT probe 664, and a CO 2 air collecting tube 665 .
  • LITT circumferential ablation probe 663 also called a LITT circumferential ablation needle core
  • OCT probe 664 an OCT probe 664
  • CO 2 air collecting tube 665 for the specific structure and process of the LITT circumferential ablation probe 663 in the LITT lateral ablation integrated probe 610.
  • Figure 7 shows an exemplary LITT lateral ablation probe prepared by the first process according to some embodiments of the present specification.
  • the LITT lateral ablation probe 700 includes a probe body 710 , a connection surface 720 and a coating 730 .
  • the connection surface 720 is the connection interface between the main body 710 and the plating layer 730 .
  • the probe body 710 is cylindrical. In some embodiments, the end (distal end) of the probe body 710 has a certain inclination angle (that is, the end surface of the probe body 710 and the axis of the probe body 710 form a certain angle, and the included angle is 0-90°, and does not include the endpoints of the range).
  • the probe body 710 is composed of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • the diameter (outer diameter) of the needle core is, for example, 550-650 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 560 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 570 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 580 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 590 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 600 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 610 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 620 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 630 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 640 ⁇ m.
  • the thickness of the hard cladding is, for example, 5-30 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 5 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 10 ⁇ m. In some embodiments, the hard cladding has a thickness of 15 ⁇ m. In some embodiments, the hard cladding has a thickness of 20 ⁇ m. In some embodiments, the hard cladding has a thickness of 25 ⁇ m. In some embodiments, the hard cladding has a thickness of 30 ⁇ m.
  • connection surface 720 uses a diamond film with specific precision (for example, 0.1 ⁇ m, 0.5 ⁇ m, 1 ⁇ m, 2 ⁇ m, 3 ⁇ m, etc.), and removes a certain numerical aperture (for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA) , 0.41NA, 0.42NA, 0.43NA, 0.44NA, 0.45NA, etc.) special step refractive index multi-mode material core, and a technology-enhanced cladding silica (TECS) hard cladding is set on the periphery as the main material. Then, a suspension of specific components is coated on the surface of the silica colloidal base film to form a smooth surface of the total reflection lens.
  • a certain numerical aperture for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA
  • a certain numerical aperture for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA,
  • the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol.
  • the suspension contains 10%-20% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 30%-40% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 20%-30% synthetic amorphous silica, 10%-20% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 30%-40% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 35%-45% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 55%-65% (propane-1,2 -diol).
  • the plating layer 730 uses noble metal target plating.
  • the precious metals may include, for example, gold, silver, and platinum group metals.
  • the coating 730 is formed by evaporation coating (for example, resistance heating evaporation coating, electron beam heating evaporation coating, induction heating evaporation coating), sputtering coating (such as magnetron sputtering coating), or ion plating.
  • the coating layer 730 is formed by magnetron sputtering coating on the surface of the connection surface 720 .
  • the plating layer 730 can be a double-layer structure, and the lower layer (near the connection surface 720) is pure silver (for example, 99.99) coated with a specific thickness (for example, 60 nanometers (nm), 80 nm, 100 nm, 120 nm, 140 nm) through magnetron coating. %, 99.999%, 99.9999% or 99.99999% pure silver), the upper layer (away from the connection surface 720) is coated with a specific thickness (for example, 120nm, 130nm, 140nm, 150nm, 160nm, 170nm, 180nm) by magnetron coating. Silicon oxide protective layer.
  • the plating layer 730 may have a single-layer structure, and is coated with pure gold (for example, 99.99%, 99.999%, 99.9999% or 99.99999%) of a specific thickness (for example, 60nm, 80nm, 100nm, 120nm, 140nm) through magnetron coating. pure gold).
  • the plating 730 is at an angle to the axis of the probe body 710 .
  • the angles are, for example, 35°, 37°, 39°, 41°, 43°, 45°, 47°, 49°, etc.
  • the above pure silver and silicon monoxide coating scheme, combined with the angle of the coating 730, can make the LITT high-power ablation laser reflectivity efficiency as high as 87%.
  • pure silver coating prevents beam leakage through the polished surface, helping to deflect the beam at wider incident angles (i.e. Lower than TIR angle range) compatibility and uniform focusing point, reflectivity, optical path deflection performance and stability are greatly improved compared to TIR.
  • the LITT lateral ablation probe 700 uses a beam with an emission angle of about 81° to uniformly emit controlled laser light to the target object to achieve ablation of the lesion tissue.
  • the preparation process of the LITT lateral ablation probe 700 includes the following steps:
  • Step S7-1 Smooth the end surface of the main body 710.
  • the end surface of the main body 710 here refers to the connection interface between the main body 710 and the plating layer 730, that is, the connection surface 720.
  • a specific precision diamond film is used to remove the core of a special step refractive index multi-mode material with a certain numerical aperture, and a technology-enhanced cladding silica (TECS) hard cladding is set as the main material on the periphery.
  • TECS technology-enhanced cladding silica
  • a suspension of specific components is applied to the surface of the silica colloidal base film to form a smooth surface at the end of the probe body 710 .
  • the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol.
  • the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the end (distal end) of the probe body 710 has a certain inclination angle, that is, the end surface of the probe body 710 forms a certain angle with the axis of the probe body 710 . If the end of the probe body 710 has no inclination angle, that is, the end surface of the probe body 710 is perpendicular to the axis of the probe body 710, a grinding step is also included. By grinding, the end surface of the probe body 710 can be aligned with the axis of the probe body 710. It forms a certain included angle, and the included angle is 0-90°, and does not include the endpoint of this range. Mechanical processing can be used to grind the end surface with a grinding wheel.
  • Step S7-2 Coating the smoothed end surface of the main body 710 to form the LITT lateral ablation probe 700.
  • the end face of the main body 710 is plated with a noble metal target.
  • the coating 730 is formed by magnetron sputtering coating on the end face of the main body 710.
  • the coating 730 can be a double-layer structure, in which case the lower layer (close to the end face) of the double-layer structure is pure silver (e.g., 99.99%, 99.999%, 99.9999% or 99.99999% pure silver) coated with a specific thickness (e.g., 60 nanometers (nm), 80nm, 100nm, 120nm, 140nm) by magnetron coating, and the upper layer (away from the end face) of the double-layer structure is a silicon monoxide protective layer coated with a specific thickness (e.g., 120nm, 130nm, 140nm, 150nm, 160nm, 170nm, 180nm) by magnetron coating.
  • a specific thickness e.g., 120nm, 130nm, 140nm, 150nm, 160n
  • the coating 730 may also be a single-layer structure, in which case it is formed by magnetron coating a specific thickness (e.g., 60nm, 80nm, 100nm, 120nm, 140nm) of pure gold (e.g., 99.99%, 99.9999%, 99.9999% or 99.99999% pure gold).
  • a specific thickness e.g. 60nm, 80nm, 100nm, 120nm, 140nm
  • pure gold e.g., 99.99%, 99.9999%, 99.9999% or 99.99999% pure gold
  • Figure 8 shows an exemplary LITT lateral ablation core prepared by the second process according to some embodiments of the present specification.
  • the LITT lateral ablation probe 800 includes a probe body 810 , a connection surface 820 , and a lens 830 .
  • the connection surface 820 is the connection interface between the main body 810 and the lens 830 .
  • the probe body 810 is cylindrical.
  • the probe body 810 is composed of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • the diameter (outer diameter) of the needle core is, for example, 550-650 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 560 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 570 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 580 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 590 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 600 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 610 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 620 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 630 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 640 ⁇ m.
  • the thickness of the hard cladding is, for example, 5-30 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 5 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 10 ⁇ m. In some embodiments, the hard cladding has a thickness of 15 ⁇ m. In some embodiments, the hard cladding has a thickness of 20 ⁇ m. In some embodiments, the hard cladding has a thickness of 25 ⁇ m. In some embodiments, the hard cladding has a thickness of 30 ⁇ m.
  • connection surface 820 uses a diamond film with specific precision (for example, 0.1 ⁇ m, 0.5 ⁇ m, 1 ⁇ m, 2 ⁇ m, 3 ⁇ m, etc.), and removes a certain numerical aperture (for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA) , 0.41NA, 0.42NA, 0.43NA, 0.44NA, 0.45NA, etc.) special step refractive index multi-mode material core, and a technology-enhanced cladding silica (TECS) hard cladding is set on the periphery as the main material. Then, a suspension of specific components is coated on the surface of the silica colloidal base film to form a smooth surface perpendicular to the end (flat end) of the probe body 810 .
  • a certain numerical aperture for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA
  • a certain numerical aperture for example, 0.41NA, 0.42NA,
  • the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol.
  • the suspension contains 10%-20% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 30%-40% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 20%-30% synthetic amorphous silica, 10%-20% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 30%-40% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 35%-45% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 55%-65% (propane-1,2 -diol).
  • lens 830 utilizes a sapphire lens.
  • lens 830 includes a right angle (90°), a base angle, and an apex angle.
  • the angle of the top corner can be determined based on the angle of the bottom corner.
  • the right angle, base angle and vertex angle satisfy a certain relationship, for example, the angle of the vertex angle is equal to 90° minus the given angle of the base angle.
  • the main body 810 and the lens 830 are both cylinders, and the lens 830 is a beveled cylinder.
  • the right angle, base angle and vertex angle here are the angles formed by each side of the lens 830 in a two-dimensional image formed from a viewing angle parallel to the oblique plane.
  • the base angle is within a certain angle range. In some embodiments, the base angle is 50°-45°. Correspondingly, the vertex angle is 40°-45°. In some embodiments, the base angle is 52°-47°. Correspondingly, the vertex angle is 38°-43°. In some embodiments, the base angle is 54°-49°. Correspondingly, the vertex angle is 36°-41°. In some embodiments, the base angle is 56°-51°. Correspondingly, the vertex angle is 34°-39°.
  • the length of the right-angled side between the base angle and the right angle of the lens 830 (i.e., the right-angled side forming the base angle), that is, the diameter of the cylindrical lens, is equal to the outer diameter of the probe body 810, which is the technology-enhanced cladding dioxide
  • the outer diameter of the silicon (TECS) hard cladding is equal to the outer diameter of the silicon (TECS) hard cladding.
  • tungsten such as tungsten wire
  • iridium such as iridium wire
  • the downlink tungsten wire or iridium wire fire polishing process is selected, that is, the welding surface is fire polished, and finally the LITT lateral ablation probe 800 is formed.
  • Fire polishing also known as flame polishing, can be done using a flame polishing machine. This process combines the lens and the lens vertex angle within a specific angle range from the horizontal plane (for example, 40°-45°, 38°-43°, 36°-41°, 34°-39°) to improve the LITT lateral Ablation Probe 800 performance.
  • the LITT lateral ablation probe 800 uses a beam with an emission angle of about 78° to uniformly emit controlled laser light to the target object to achieve ablation of the lesion tissue.
  • the lens 830 may also be a beveled hemispherical lens (such as a sapphire hemispherical lens).
  • the diameter of the beveled hemispherical lens is, for example, 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1 mm, etc.
  • the lens 830 may also be a beveled semi-ellipsoidal lens (such as a sapphire semi-ellipsoidal lens).
  • the long semi-axis of the beveled semi-ellipsoidal lens is, for example, 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1 mm, 1.1 mm, 1.2 mm, etc.
  • the flattening of the beveled semi-ellipsoidal lens is, for example, 1/298, 1/250, 1/200, 1/150, 1/100, 1/50, etc.
  • the preparation process of the LITT lateral ablation probe 800 includes the following steps:
  • Step S8-1 Smooth the end surface of the main body 810.
  • the end surface of the main body 810 refers to the connection interface between the main body 810 and the lens 830, that is, the connection surface 820.
  • the end surface of the main body 810 is perpendicular to the axis of the main body 810 .
  • a specific precision diamond film is used to remove the core of a special step refractive index multi-mode material with a certain numerical aperture, and a technology-enhanced cladding silica (TECS) hard cladding is set as the main material on the periphery.
  • TECS technology-enhanced cladding silica
  • a suspension of specific components is coated on the surface of the silica colloidal base film to form a smooth surface at the end of the probe body 810 .
  • the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol.
  • the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • Step S8-2 Weld the main body 810 and the lens 830 to form the LITT lateral ablation probe 800.
  • the main body 810 and the lens 830 are welded using a specific high-temperature treatment method to establish a stable connection between the lens 830 and the main body 810 .
  • body 810 and lens 830 may be welded by arc welding.
  • high-temperature melting of materials such as tungsten (such as tungsten wire) and iridium (such as iridium wire) can also be used to weld the main body 810 and the lens 830 .
  • tungsten wire or iridium a tungsten wire or iridium wire fire polishing process is selected, that is, the welding surface is fire polished, and finally the LITT lateral ablation probe 800 is formed.
  • Figure 9 illustrates an exemplary LITT circumferential ablation probe in accordance with some embodiments of the present specification.
  • LITT circumferential ablation probe 900 includes probe body 910 .
  • the probe body 910 is composed of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • the diameter (outer diameter) of the needle core is, for example, 550-650 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 560 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 570 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 580 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 590 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 600 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 610 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 620 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 630 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 640 ⁇ m.
  • the thickness of the hard cladding is, for example, 5-30 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 5 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 10 ⁇ m. In some embodiments, the hard cladding has a thickness of 15 ⁇ m. In some embodiments, the hard cladding has a thickness of 20 ⁇ m. In some embodiments, the hard cladding has a thickness of 25 ⁇ m. In some embodiments, the hard cladding has a thickness of 30 ⁇ m.
  • a tapered surface 920 is provided at the distal end of the probe body 910 (the end close to the target object).
  • the diameter of the tapered surface gradually decreases from the initial diameter to the preset diameter.
  • the initial diameter is the sum of the diameter of the needle core and the thickness of the cladding. Exemplarily, the initial diameter is 630 ⁇ m.
  • the preset diameter is the diameter of the distal end of the probe body 910 .
  • the preset diameter is 50-150 ⁇ m. In some embodiments, the preset diameter is 60 ⁇ m. In some embodiments, the preset diameter is 70 ⁇ m. In some embodiments, the preset diameter is 80 ⁇ m. In some embodiments, the preset diameter is 90 ⁇ m.
  • the preset diameter is 100 ⁇ m. In some embodiments, the preset diameter is 110 ⁇ m. In some embodiments, the preset diameter is 120 ⁇ m. In some embodiments, the preset diameter is 130 ⁇ m. In some embodiments, the preset diameter is 140 ⁇ m.
  • Grooves are provided on the tapered surface 920 .
  • the laser light directed to the LITT circumferential ablation probe 900 can be emitted from the groove to treat the target object and achieve ablation of the lesion tissue.
  • the grooves are evenly (dispersed) distributed along the tapered surface 920 in a certain pattern shape (for example, thread shape) and do not overlap with each other. LITT circumferential ablation probe, also known as LITT circumferential diffusion ablation probe.
  • the groove has a certain depth. Exemplarily, the depth of the groove is 5-35 ⁇ m. In some embodiments, the groove has a depth of 10 ⁇ m. In some embodiments, the groove has a depth of 15 ⁇ m. In some embodiments, the groove has a depth of 20 ⁇ m. In some embodiments, the groove has a depth of 25 ⁇ m. In some embodiments, the groove has a depth of 30 ⁇ m.
  • the distribution pattern of the grooves is a single thread shape (spiral shape), a multi-thread cross shape (for example, a double thread cross, as shown in Figure 9), a rhombus grid shape, a honeycomb shape, etc., or combination thereof.
  • the single thread shape, multi-thread cross shape, rhombus grid shape, and honeycomb shape listed above are only specific examples and do not limit the specific distribution pattern of the grooves. It can also be any other reasonable pattern. It is required that the specific distribution shape of the grooves is evenly (dispersed) distributed along the tapered surface 920 and does not overlap.
  • the tapered surface 920 and the evenly distributed grooves arranged in a certain pattern on the tapered surface 920 can be formed by engraving with an optoelectronic device (for example, an optical machine).
  • an optoelectronic device for example, an optical machine
  • the tapered surface 920 and the cross-threaded grooves provided thereon can be carved and formed by the optoelectronic equipment and method described in FIGS. 10 and 11 , respectively.
  • the tapered surface 920 and the groove provided thereon can also be processed by other methods, such as mechanical processing.
  • Figure 10 is a schematic diagram of an exemplary tapered surface processing according to some embodiments of the present specification.
  • the tapered surface 920 is carved and formed by the tapered engraving device 1000 .
  • the cone engraving equipment 1000 includes a terminal 1001, a laser controller 1002, a laser 1003, reflectors 1004-1 and 1004-2, a shutter 1005, a shutter controller 1006, a laser power attenuator 1007, a diffraction beam splitting lens unit 1008, and a focusing lens unit. 1009, slide rail 1010, fixing device 1011, motion driver 1012, and motion drive controller 1013.
  • the terminal 1001 connects to and controls the laser controller 1002, the shutter controller 1006 and the motion drive controller 1013.
  • the laser controller 1002 connects and controls the laser 1003 to emit laser light.
  • the terminal 1101 may be, for example, a computer.
  • Laser 1003 may be a high power CO2 continuous wave laser.
  • Reflectors 1004-1 and 1004-2 can use silver mirrors.
  • Shutter 1005 may be an electric shutter.
  • the shutter controller 1006 is connected to and controls the switch of the shutter 1005 to control the opening and closing of the laser light path.
  • the diffraction beam splitting lens unit 1008 and the focusing lens unit 1009 are used to split the laser beam to form two laser beams and focus them respectively.
  • the focusing lens unit 1009 may be, for example, a zinc selenide lens.
  • the motion drive controller 1013 is connected to and controls the motion driver 1012 to drive the workpiece 1015 to be tapered to move, for example, translation and/or rotation.
  • the process of carving the cone surface 920 by the cone carving device 1000 includes the following steps:
  • Step S10-1 Fix both ends of the workpiece 1015 to be carved to the slide rail 1010 and the fixing device 1011 respectively.
  • the fixing device 1011 is connected to the motion driver 1012 .
  • Fixing device 1011 may be a clamp. The clamp can clamp and fix one end of the workpiece 1015 to be tapered.
  • Step S10-2 Use the terminal 1001 to cause the laser controller 1002 to control the laser 1003 to emit laser.
  • Laser 1003 generates laser light with a specific power and wavelength.
  • the power of the generated laser is, for example, in the range of 20-40W. In some embodiments, the power of the laser generated is 25W. In some embodiments, the power of the laser generated is 30W. In some embodiments, the power of the laser generated is 35W.
  • the wavelength of the laser produced is approximately 10600nm.
  • the laser light is reflected to the shutter 1005 via the mirror 1004-1.
  • Step S10-3 The shutter controller 1006 controls the shutter 1005 to open through the terminal 1001, and the laser is emitted to the laser power attenuator 1007 for power attenuation processing.
  • the laser power attenuator 1007 attenuates the input laser power by a certain proportion, for example, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80%, 90%, etc., that is, performs power attenuation processing. .
  • the laser power output by the laser power attenuator 1007 (that is, the laser power after attenuation processing) is within a certain range, for example, 3-20W.
  • the laser power after attenuation treatment is 6-15W.
  • the laser power after attenuation treatment is 6.6-11.2W.
  • the diffraction beam splitting lens unit 1008 may be a beam splitting lens customized for the laser wavelength.
  • Step S10 - 4 The laser beam after power attenuation processing is split into two laser beams by the diffraction beam splitting lens unit 1008 , and the two laser beams are focused onto the surface of the workpiece 1015 to be coned by the focusing lens unit 1009 .
  • the workpiece 1015 to be tapered includes a fiber core and a hard cladding around the core.
  • the core is made of pure silica material.
  • the hard cladding around the core is made of Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • the two laser beams respectively form light spots 1014-1 and 1014-2 on the surface of the workpiece 1015 to be carved.
  • the light spots 1014-1 and 1014-2 are focused on the peripheral hard cladding of the workpiece 1015 to be carved.
  • Step S10-5 Use the terminal 1001 to cause the motion drive controller 1013 to control the motion driver 1012 to drive the movement of the workpiece 1015 to be tapered.
  • the light spots 1014-1 and 1014-2 formed by the laser are engraved on the surface of the workpiece 1015 to be carved with a cone, and finally a conical surface 920 is formed.
  • FIG. 11 is a schematic diagram of processing of exemplary cross-threaded grooves according to some embodiments of the present specification.
  • cross-threaded grooves are carved and formed on the surface of the workpiece 1110 to be carved by the engraving device 1100 .
  • the workpiece 1110 to be carved is a workpiece with a tapered surface 920 that has been processed through the above steps S10-1 to S10-5.
  • the engraving equipment 1100 includes a terminal 1101, a laser controller 1102, a laser 1103, a reflector 1104, a lens group 1005, a slide rail 1106, a fixing device 1107, a motion driver 1108, and a motion drive controller 1109.
  • the terminal 1101 connects and controls the laser controller 1102 and the motion drive controller 1109.
  • the terminal 1101 may be, for example, a computer.
  • the laser controller 1102 connects and controls the laser 1103 to emit laser light.
  • Laser 1103 may be a high power CO2 continuous wave laser.
  • the reflector 1104 may be a silver mirror.
  • Lens group 1005 may include one or more lenses.
  • the one or more lenses include concave lenses and/or convex lenses.
  • the motion drive controller 1109 is connected to and controls the motion driver 1108 to drive the workpiece 1110 to be carved to move, for example, translation and/or rotation.
  • the process of engraving cross-threaded grooves by the engraving device 1100 includes the following steps:
  • Step S11-1 Fix both ends of the workpiece 1110 to be carved to the slide rail 1106 and the fixing device 1107 respectively.
  • the fixation device 1107 is connected to the motion driver 1108 .
  • Fixing device 1107 may be a clamp. The clamp can clamp and fix one end of the workpiece 1110 to be carved.
  • Step S11 - 2 The terminal 1101 enables the laser controller 1102 to control the laser 1103 to emit laser light.
  • the laser generated by the laser 1103 has a specific power and wavelength.
  • the power of the generated laser is, for example, in the range of 20-40W. In some embodiments, the power of the generated laser is 25W. In some embodiments, the power of the generated laser is 30W. In some embodiments, the power of the generated laser is 35W.
  • the wavelength of the generated laser is about 10600nm.
  • the laser 1103 can be a high-power CO2 continuous wave laser.
  • the damage threshold of the workpiece 1110 to be engraved is about 250kW/ cm2 ; for the pulse wave of the high-power CO2 continuous wave laser (for example, a pulse wave of 10ns), the damage threshold of the workpiece 1110 to be engraved is about 1GW/ cm2 .
  • Step S11-3 The laser is focused on the surface of the workpiece 1110 to be carved through the lens group 1105.
  • the laser passes through the lens group 1105 and forms a light spot of specific energy and size on the conical surface of the workpiece 1110 to be carved.
  • the diameter of the light spot is 30-60 ⁇ m.
  • the spot diameter is 35 ⁇ m.
  • the diameter of the light spot is 40 ⁇ m.
  • the spot diameter is 45 ⁇ m.
  • the diameter of the light spot is 50 ⁇ m.
  • the spot diameter is 55 ⁇ m.
  • the energy of the light spot is higher than the irradiance of the surface material ablation of the workpiece 1110 to be carved.
  • the irradiance of the surface material of the workpiece 1110 to be carved is close to the irradiance of glass ablation, which is 3.1 ⁇ 10 5 W/cm 2 .
  • the lens group 1105 may include a first concave lens, a first convex lens, and a second concave lens arranged in sequence.
  • the first concave lens and the first convex lens are used to expand the diameter of the laser beam to the first diameter
  • the second concave lens is used to focus the laser beam of the first diameter onto the surface of the workpiece 1110 to be engraved to form the above-mentioned light spot.
  • Step S11-4 Use the terminal 1101 to cause the motion drive controller 1109 to control the motion driver 1108 to drive the workpiece 1110 to be engraved to move.
  • the light spot formed by the laser engraves on the surface of the workpiece 1110 to be carved, and finally forms grooves distributed in a cross-thread shape on the conical surface of the workpiece 1110 to be carved.
  • an air cooling system can be used to blow the engraved grooves and remove particles (such as dust, impurities) in and around the grooves. Molten materials, etc., keep the surface of the processing area clean.
  • the LITT circumferential ablation probe 900 engraved by the optoelectronic equipment and method described in Figures 10 and 11 has a certain pattern (for example, cross threads) of grooves evenly (diffuse) distributed along the tapered surface 920, so the LITT circumferential
  • the vector light energy distributed to the ablation probe 900 is more evenly distributed, and combined with the temperature measurement mechanism of the above-mentioned temperature measurement element, the ablation of the surrounding tissue is more uniform and complete.
  • the tissue thermal characteristics and thermal damage algorithm based on the LITT circumferential ablation probe 900 the protection of healthy tissue during the operation and the ablation effect of ablation pathology have been significantly improved.
  • Figure 12 is a schematic diagram of vector light energy distribution of a LITT circumferential ablation probe tested according to some embodiments of this specification.
  • the uniformity of the vector light energy distribution of the LITT circumferential ablation probe 900 can be tested by the LITT probe polarity testing device 1200 .
  • the uniformity of the vector light energy distribution of the LITT circumferential ablation probe 900 can be characterized by the polar intensity of the circumferential spatial light distribution of the LITT circumferential ablation probe 900 at different heights.
  • the LITT probe polarity testing device 1200 includes a laser 1201, a fiber coupler 1202, a LITT circumferential ablation integrated probe 1203, an aperture 1204, a laser measurement sensor 1205, a terminal 1206, a motion driver 1207, and a motion drive controller 1208.
  • the laser 1201 may be a helium-neon laser.
  • the helium-neon laser is a helium-neon laser emitting a laser wavelength of 632.8 nm.
  • the aperture 1204 is used to limit the propagation of the light beam.
  • the aperture 1204 is installed in front of the laser measurement sensor 1205 to limit the laser received by the laser measurement sensor 1205, for example, so that the laser measurement sensor 1205 can only receive lasers in a specific direction.
  • the aperture 1204 may be an aperture aperture, a slit aperture, etc.
  • the aperture 1204 may be a slit aperture.
  • the size of the slit aperture i.e., the width of the slit
  • the size of the slit aperture is 0.2 mm. In some embodiments, the size of the slit aperture is 0.3 mm. In some embodiments, the size of the slit aperture is 0.4 mm.
  • the laser measurement sensor 1205 is used to receive laser light and generate a corresponding electrical signal to characterize the intensity of the received laser light. In some embodiments, the laser measurement sensor 1205 may be a circular geometry photodiode laser measurement sensor or other sensors that can measure laser intensity.
  • the terminal 1206 is connected to and controls the laser measurement sensor 1205 and the motion drive controller 1208. The terminal 1206 can be, for example, a computer.
  • the aperture 1204 and the laser measurement sensor 1205 are fixedly connected to the motion driver 1207.
  • the motion drive controller 1208 is connected to and controls the motion driver 1207 to drive the aperture 1204 and the laser measurement sensor 1205 to move, for example, translate and/or rotate.
  • the process of testing the uniformity of the vector light energy distribution of the LITT circumferential ablation probe 900 through the LITT probe polarity testing device 1200 includes the following steps:
  • Step S12-1 Obtain the signal output by the laser measurement sensor 1205 through the terminal 1206, and generate the laser polarity intensity in a specific direction.
  • the laser 1201 generates laser light (for example, visible light) and conducts it to the optical fiber coupler 1202 via a spatial optical path (such as an optical fiber).
  • Fiber optic coupler 1202 couples to the LITT probe channel of the LITT circumferential ablation integrated probe.
  • the laser light is transmitted to the LITT circumferential ablation probe 900 and passes through the circumferentially uniformly distributed grooves on the LITT circumferential ablation probe 900 to emit vector light energy in a 360-degree dispersion.
  • the vector light energy is limited by the aperture 1204 and enters the laser measurement sensor 1205.
  • the laser measurement sensor 1205 receives the incident laser and generates a corresponding electrical signal to represent the intensity of the received laser. This intensity is the laser polarity intensity of the aperture 1204 and the laser measurement sensor 1205 in this orientation.
  • Step S12-2 The motion drive controller 1208 controls the motion driver 1207 through the terminal 1206 to drive the aperture 1204 and the laser measurement sensor 1205 to move circumferentially and axially along the tapered surface of the LITT circumferential ablation probe 900 , thereby obtaining the intensity distribution of the laser in the entire space (referred to as spatial intensity distribution).
  • the entire space refers to the circumference (360 degrees) and axial direction (overall length) of the LITT circumferential ablation probe 900 .
  • the motion driver 1207 is controlled by the motion drive controller 1208 to perform rotational circular motion.
  • the aperture 1204 and the laser measurement sensor 1205 are fixedly connected to the motion driver 1207. Therefore, the aperture 1204 and the laser measurement sensor 1205 will make a circle around the LITT circumferential ablation probe 900. Movement, and then based on the method for determining the single-point polarity intensity in the above step S12-1, the circumferential vector light distribution polarity intensity of the LITT circumferential ablation probe 900 is obtained.
  • the motion driver 1207 is used to adjust the positions of the aperture 1204 and the laser measurement sensor 1205 relative to the length direction of the LITT circumferential ablation probe 900 (which can also be referred to as different heights) to obtain the values of the LITT circumferential ablation probe 900 at different heights.
  • the polar intensity of the circumferential vector light is distributed, thereby obtaining the intensity distribution of the laser (vector light) in the entire space.
  • the LITT circumferential ablation probe 900 formed by the photoelectric equipment and method described in Figures 10 and 11 was tested using the methods described in S12-1 and S12-2 above.
  • the vector light energy distribution is very uniform. Therefore, the LITT circumferential ablation probe 900 has better performance and therapeutic effect.
  • Figure 13 is a schematic diagram of temperature measurement using a thermocouple according to some embodiments of this specification.
  • the temperature measurement element (temperature measurement element 611 or 661), such as the thermocouple 1303, can be disposed in the integrated probe (LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660) to Measure the temperature of the LITT probe and/or target object.
  • the integrated probe LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660
  • the thermocouple 1303 may be connected to the power collection module 1302.
  • the power supply collection module 1302 is further connected to the terminal 1301.
  • the power supply acquisition module 1302 provides power to the thermocouple 1303 and transmits the temperature collected during the operation of the thermocouple 1303 to the terminal 1301.
  • Terminal 1301 may be, for example, a computer.
  • the thermocouple 1303 can be a K-type thermocouple, a T-type thermocouple, an E-type thermocouple, etc.
  • the thermocouple 1303 is a K-type thermocouple.
  • the parameters of the K-type thermocouple may be a diameter of 40-60 ⁇ m, a resistance of 46-55 ohms ( ⁇ ), and a measurement accuracy of ⁇ 0.5-2 degrees Celsius (°C).
  • the parameters of the K-type thermocouple are 50 ⁇ m in diameter, 51 ⁇ in resistance, and ⁇ 1.2°C in measurement accuracy.
  • thermocouple 1303 When the LITT probe is working, the thermocouple 1303 is close to the target object. At the same time, the LITT probe emits a laser ablation signal, which will also affect the thermocouple 1303.
  • the thermocouple 1303 is connected to the terminal 1301 through the power supply collection module 1302, and collects and records the temperature changes of the target object and/or LITT probe in real time. Thermocouple 1303 is used to measure the temperature of the target object and/or LITT probe. Because it is close to the tissue and probe, the temperature measurement results are more accurate than the remote temperature measurement of MRTI nuclear magnetic thermal imaging.
  • Figure 14 is a schematic diagram of temperature measurement using an FBG sensor according to some embodiments of this specification.
  • the temperature measurement element (temperature measurement element 611 or 661), such as the FBG sensor 1404-1, can be disposed in the integrated probe (LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660) , to measure the temperature of the LITT probe and/or target object.
  • the integrated probe LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660
  • the system When actually applied to temperature measurement, the system includes a terminal 1401, an ASE laser 1402, a circulator 1403, an FBG sensor 1404-1, a telecommunications spectrum analyzer 1405, and a temperature controller 1406.
  • the terminal 1401 may be, for example, a computer.
  • the ASE Laser 1402 has ultra wide bandwidth.
  • the ASE laser 1402 may be a three-in-one S, C and L band, 140nm ultra-wideband, 1530nm central wavelength ASE laser.
  • Circulator 1403 may be an ultra-bandwidth multimode high power circulator.
  • Telecommunications spectrum analyzer 1405 is a telecommunications spectrum analyzer with an analysis range of 600-1700nm.
  • Multiphysics software performs numerical calculations to predict the spatial distribution of intracranial interstitial tissue temperature and the degree of thermal degeneration set by the physician during LITT.
  • the geometry used for the simulation uses the LITT circumferential ablation probe 900 of the present invention (as shown in the figure).
  • the distal end of the LITT circumferential ablation probe 900 is sleeved with the distal glass through the main body 910 PEEK or polycarbonate PC tube.
  • ⁇ (kg/m 3 ) tissue density
  • c (J/kg ⁇ K) tissue specific heat
  • K (W/m ⁇ K) tissue thermal conductivity
  • T (°C) tissue temperature. Due to the use of in vitro model development, the effects of blood perfusion and metabolic heat production are actually 0;
  • Qi (W/m 3 ) is the laser-induced heat source.
  • preliminary angular measurements confirmed that the laser intensity is delivered in two directions: the radial emitted power of the diffusion part P1 (89% of the incident laser power in W) and the forward emitted power of the fiber tip P2 (89% of the incident laser power in W). 11%), based on these settings, the thermal response of the tissue during LITT irradiation is quantified as:
  • ⁇ 0 (cm -1 ) is the absorption coefficient of the tissue
  • ⁇ s (cm -1 ) is the scattering coefficient of the tissue
  • r (m) is the radial distance from the diffuser surface
  • l (m) is the diffuser length .
  • ⁇ ( ⁇ m) is the spot size of the laser beam and z (m) is the axial depth in the tissue.
  • the heat source is converted and quantified as:
  • the initial temperature of the entire tissue is set to 20°C, and the outer surface of the tissue is insulated (i.e. in is the direction of heat flow).
  • the Arrhenius parameter is used to determine the degree of thermal damage, mainly due to the temperature dependence of molecular reaction rates.
  • Table 1 shows the main parameter constant types for the optical properties of the target organ at 980 nm or 1064 nm, which are assumed to be constant during LITT treatment):
  • ⁇ S is affected by the temperature change of thermal expansion or contraction of the grating period and the thermo-optical effect (thermal-induced change of n eff ), which makes FBG can be used as a temperature sensing element.
  • the FBG sensor 1404-1 is obtained by combining the preparation process of FBG with the aforementioned raw materials, which allows the refractive index of the optical fiber core to be periodically modulated. Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other. In turn, the input beam only experiences strong reflections at specific wavelengths determined by certain phase matching conditions. The reflected wavelength is called the Bragg wavelength ( ⁇ S ) of the FBG, and the phase matching condition is called the Bragg condition.
  • the quantification of ⁇ S is:
  • ⁇ T T H - T 0 , T 0 and TH are the reference and high temperatures applied to the FBG, respectively.
  • ⁇ S0 is the Bragg wavelength of FBG at T 0
  • ⁇ ⁇ and ⁇ n are the thermal expansion and thermo-optical coefficients of the monopole fiber produced as FBG, respectively.
  • the Bragg wavelength drift ⁇ S induced by the temperature change ⁇ T is quantified as:
  • the thermal sensitivity S of the FBG is quantified as:
  • the FBG sensor 1404-1 can monitor the interstitial tissue temperature during LITT laser irradiation in real time.
  • This calibration requires the temperature range under the control of the temperature controller 1406 in the FBG temperature measurement calibration mode (for example, -50°C to 180°C, -40°C to 150°C, -30°C to 120°C, -20°C to 100°C °C, etc.), perform this static calibration.
  • the system includes terminal 1401, ASE laser 1402, circulator 1403, FBG sensor 1404-2, telecommunications spectrum analyzer 1405, and temperature controller 1406.
  • the FBG sensor 1404-2 is placed in the temperature controller 1406 that can control the temperature between -40°C and 150°C.
  • the ASE laser 1402 may be an ultra-wideband ASE laser, and its broadband light reaches the FBG sensor 1404-2 through the circulator 1403.
  • the reflection signal of the FBG sensor 1404-2 enters the telecommunications spectrum analyzer 1405 through the circulator 1403, and the telecommunications spectrum analyzer 1405 is used to monitor the reflection spectrum of the FBG sensor 1404-2.
  • the calibration test is performed within a specific temperature range (for example, 10°C-80°C, 20°C-100°C, 30°C-120°C), with each temperature interval being 10°C and lasting 5 hours.
  • Figure 15 is an exemplary OCT probe according to some embodiments of the present specification.
  • the OCT probe 1500 has a long working distance and is suitable for assisting LITT in ablating large-sized target objects (for example, cancerous tissue).
  • the OCT probe 1500 includes an input port 1501, a first lens 1502, a second lens 1504, a beam deflection unit 1506, a spring torsion coil 1508, an optical sleeve 1510 and a filling body 1512.
  • the two end surfaces of the second lens 1504 are respectively welded to the first lens 1502 and the beam deflection unit 1506 through high-temperature fusion of specific materials, such as tungsten and iridium, and are fire polished to form a welded surface, so that the second lens 1504 is connected to the first lens 1504 .
  • the lens 1502 and the beam deflection unit 1506 are fixedly connected.
  • the light beam emitted by the light source of the OCT equipment enters the OCT probe 1500 through a specific optical path, such as the optical fiber slip ring device 212 and the input port 1501 (eg, single-mode optical fiber).
  • the input port 1501 is configured to input the light beam emitted by the light source to the OCT probe 1500 .
  • the light beam entering the OCT probe 1500 passes through the first lens 1502 and the second lens 1504 in sequence, and is deflected by the light beam deflection unit 1506 and exits the OCT probe 1500 .
  • the light beam emerging from the OCT probe 1500 may be used to illuminate the target object.
  • the first lens 1502 is configured to expand the light beam incident on the OCT probe 1500 (first lens 1502).
  • the incident light beam is a parallel light beam
  • the first lens 1502 can expand the parallel light beam.
  • the expanded beam has a certain divergence angle (also called beam expansion angle).
  • the first lens 1502 is cylindrical.
  • first lens 1502 is a coreless lens.
  • the beam expansion angle of the coreless lens is 2 ⁇ , where ⁇ is, for example, 5°, 10°, 15°, 20°, 25°, etc.
  • the coreless lens has a certain length b.
  • the focal length and focal spot size of the OCT probe 1500 are related to the length b of the coreless lens.
  • the second lens 1504 is disposed at the rear stage (rear end) of the first lens 1502 , and the light beam emitted from the first lens 1502 enters the second lens 1504 .
  • the second lens 1504 is configured to focus the light beam exiting the first lens 1502 to generate an exit spectrum with a certain focal length.
  • the second lens 1504 can also achromatically disperse the light beam exiting the first lens.
  • the second lens 1504 may be a micro-plano-convex spherical cylindrical lens.
  • the micro-plano-convex spherical cylindrical lens has a starting end and an end along the lens axis (for example, the direction of light beam propagation in the figure).
  • the starting end here is the end surface where the light beam is incident, and the end is the end surface where the light beam is emitted.
  • the starting end of the micro-plano-convex spherical cylindrical lens is a flat surface and the end is a convex spherical surface.
  • the part between the beginning and the end is a cylinder.
  • the cylinder has a certain cylinder diameter (ie, the cross-sectional diameter of the cylinder).
  • the cylinder diameter is, for example, 500 ⁇ m, 520 ⁇ m, 540 ⁇ m, 560 ⁇ m, 580 ⁇ m, 600 ⁇ m, 620 ⁇ m, etc.
  • the diameter of the cylinder is 560 ⁇ m, which can ensure that the light beam passes completely. Anything greater than or less than 560 ⁇ m will compromise the optical path performance (for example, less than 560 ⁇ m will cause the diffused optical path to be unable to be fully mechanically compatible with the OCT probe 1500, resulting in serious insertion loss and loss of imaging bandwidth).
  • the optical curvature r of the terminal convex spherical surface of the micro plano-convex spherical cylindrical lens is, for example, -1.5mm, -1.6mm, -1.7mm, -1.8mm, -1.9mm, -2mm, -2.1mm, etc.
  • the optical curvature r of the terminal convex spherical surface of the micro plano-convex spherical cylindrical lens is -1.8 mm.
  • the -1.8mm curvature is the key to ensuring that the OCT probe 1500 exceeds the effective working distance of 1cm. Otherwise, the focal length will shift inward to reduce the working distance, expand the spot, reduce lateral resolution, and reduce imaging quality.
  • the materials used in the micro plano-convex spherical cylindrical lens are, for example, N-LAF3, SF11, N-SF11 and other optical materials.
  • the material used in the micro plano-convex spherical cylindrical lens is N-LAF3.
  • the micro-plano-convex spherical cylindrical lens has a certain refractive index n.
  • the refractive index n is, for example, 1.3, 1.4, 1.5, 1.6, 1.7, 1.8, etc.
  • the starting end of the second lens 1504 (ie, the beam incident end surface) is a polished surface and has a certain angle.
  • the angle here is the angle between the vertical plane of the axis of the second lens 1504 and the starting end surface of the second lens 1504 .
  • the angles are, for example, 0°, 2°, 4°, 6°, 8°, 10°, etc. In some embodiments, the angle is 0° or 8°. When the angle is 0°, the mechanical stress performance can be increased after fire polishing of the welding surface; when the angle is 8°, the TIR pollution value of the lens welding surface can be significantly reduced and the insertion loss is reduced.
  • the beam deflection unit 1506 is disposed at the rear stage (rear end) of the second lens, and the beam exiting the second lens 1504 enters the beam deflection unit 1506 .
  • the beam deflection unit 1506 is configured to deflect the light beam that exits the second lens 1504 , and the deflected light beam exits the OCT probe 1500 .
  • the beam deflection unit 1506 includes a cylindrical core and a hard cladding located around the core.
  • the beam deflection unit 1506 includes a beveled end surface, and the beveled end surface is coated with a metal plating layer.
  • the beam deflection unit 1506 may be similar to the LITT lateral ablation probe 700 described in FIG. 7 .
  • the beam deflection unit 1506 includes a main body, a connection surface and a coating.
  • the main body includes a fiber core and a hard cladding located on the periphery of the fiber core.
  • the core is made of pure silica material.
  • the hard cladding is made of Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • the end face of the main body has a certain inclination angle, which is the beveled end face. At this time, the end face of the main body forms a certain angle with the axis of the main body.
  • the included angle is 0-90°, and does not include this range. endpoint.
  • the connection surface is the connection interface between the chamfered end surface and the plating layer.
  • the connecting surface is formed by smoothing the chamfered end surface.
  • the connection surface is coated with the plating layer (for example, a noble metal plating layer).
  • the precious metals may include, for example, gold, silver, and platinum group metals.
  • the coating can be formed on the surface of the connection surface by, for example, magnetron sputtering coating.
  • the angle between the coating and the axis of the body is, for example, 35°, 37°, 39°, 41°, 43°, 45°, 47°, 49°, etc.
  • the truncated axial cylinder of the beam deflection unit 1506 has a certain length.
  • the truncated axial cylinder is the cylinder between the beam incident end surface of the beam deflection unit 1506 and the bevel point of the beveled end surface.
  • the bevel point is the point on the bevel end surface that is closest to the beam incident end surface of the beam deflection unit 1506 .
  • the cut-off axial cylinder length is, for example, 2 ⁇ m, 5 ⁇ m, 8 ⁇ m, 10 ⁇ m, etc. In some embodiments, the length of the truncated axial cylinder is 5 ⁇ m, in which case the spectral deflection effect of the beam deflection unit 1506 is better.
  • the spring torsion coil 1508 is disposed at the front end of the OCT probe 1500 .
  • one end of the spring torsion coil 1508 is in contact with the starting end of the second lens 1504 .
  • the spring torsion coil 1508 provides rotational torsion support for the OCT probe 1500 through its properties of lifting, compressing and twisting.
  • optical sleeve 1510 is used to accommodate the spring torsion coil 1508, the first lens 1502, the second lens 1504 and the beam deflection unit 1506.
  • optical tube 1510 is a tubular optical element, such as tubular optical glass.
  • the spring torsion coil 1508, the first lens 1502, the second lens 1504 and the beam deflection unit 1506 are arranged in the optical tube 1510 in sequence.
  • the optical sleeve 1510 has light transmittance. The light beam emitted through the beam deflection unit 1506 passes through the optical sleeve 1510 and exits the OCT probe 1500.
  • the filling body 1512 is filled inside the optical sleeve 1510 .
  • the filling body 1512 is optical glue, which solidifies after a certain period of time after filling.
  • the filling body 1512 can be filled between the first lens 1502 , the second lens 1504 , the beam deflection unit 1506 and the optical sleeve 1510 In the gap, the first lens 1502, the second lens 1504 and the beam deflection unit 1506 can be fixed relative to the optical tube 1510.
  • the refractive index of the filling body 1512 is much smaller than the refractive index of the second lens (for example, the micro-plano-convex spherical cylindrical lens) to avoid affecting the propagation of the light beam in the OCT probe 1500 Make an impact.
  • the second lens for example, the micro-plano-convex spherical cylindrical lens
  • the ABCD optical Gaussian transmission matrix T of the OCT probe 1500 can be expressed as:
  • the Gaussian transmission moment M at any length z of the OCT probe 1500 emission spectrum can be expressed as the formula:
  • the central wave number of the light source is defined as k 0
  • the wavelength under different traversals i in the spectral bandwidth range is ⁇
  • the probe focal length under different b values is:
  • the focus spot radius under different b values is:
  • the focal length and focus spot size of the OCT probe 1500 can be adjusted, thereby changing the working distance of the OCT probe 1500 to make it Can be applied to pathological imaging of large-sized tissues.
  • Figure 16 is a schematic diagram of preparing an FBG sensor according to some embodiments of this specification.
  • the FBG sensor is obtained by irradiating specially prepared raw materials through FBG irradiation equipment 1600 .
  • the specially prepared raw materials must meet specific parameter conditions.
  • the parameter conditions are as mentioned above and will not be repeated here.
  • the FBG irradiation equipment 1600 includes a terminal 1601, a laser controller 1602, a laser 1603, beam correction devices 1604-1 and 1604-2, a slit diaphragm 1605, a UV coating lens 1606, a phase mask 1607, and a slide rail 1609. Fixation device 1610, motion driver 1611, and motion drive controller 1612.
  • the terminal 1601 connects and controls the laser controller 1602 and the motion drive controller 1612.
  • Terminal 1601 may be, for example, a computer.
  • the laser controller 1602 connects and controls the laser 1603 to emit laser light.
  • Laser 1603 may be an excimer pulsed laser with a specific characteristic wavelength (eg, 248 nm).
  • the power of the laser it generates can be, for example, 8W, 10W, 12W, 15W, etc.; its pulse frequency can be, for example, 90Hz, 100Hz, 120Hz, etc.; its pulse energy can be, for example, 100mJ, 120mJ, 140mJ etc.
  • the laser generated by the laser 1603 is a flat-top laser beam with almost uniform flux (energy density).
  • the spot emission of the laser beam is characterized by a rectangular flat-top, and its central wavelength is, for example, 248 nm; its pulse duration is , for example, 10ns, 12ns, 15ns, 20ns, etc.; the rectangular flat top is, for example, 4 ⁇ 1mm 2 , 6 ⁇ 1.5mm 2 , 10 ⁇ 3mm 2 , etc.; its divergence angle is, for example, 2 ⁇ 1mrad 2 , 3 ⁇ 2mrad 2 , 4 ⁇ 2mrad 2 , etc.
  • the beam correction devices 1604-1 and 1604-2 are used to deflect the beam and correct the optical path.
  • the beam correction devices 1604-1 and 1604-2 are both 248 nm characteristic wavelength excimer laser 45° line mirrors, used to deflect the laser light generated by the laser 1603 at 45° and perform optical path correction.
  • the slit diaphragm 1605 is used to limit the propagation of light beams in specific directions.
  • the size of the slit aperture 1605 ie, the width of the slit
  • the size of slit aperture 1605 is, for example, 2-6 mm. In some embodiments, the size of slit aperture 1605 is 2 mm. In some embodiments, slit aperture 1605 measures 3 mm. In some embodiments, slit aperture 1605 measures 4.5 mm. In some embodiments, slit aperture 1605 measures 6 mm. In this embodiment, the slit diaphragm 1605 is a mechanical slit device with an adjustable width of 4.5 mm.
  • the ultraviolet coated lens 1606 is used to focus the laser beam in the ultraviolet region.
  • the UV-coated lens 1606 may be a UV-coated fused silica plano-convex cylindrical lens.
  • the UV-coated fused silica plano-convex cylindrical lens can focus the light beam (focal length is, for example, 150mm, 200mm, 250mm, etc.) to the phase mask 1607.
  • the characteristic wavelength of the UV-coated fused silica plano-convex cylindrical lens is 100-600nm. In some embodiments, the characteristic wavelength of the UV-coated fused silica plano-convex cylindrical lens is 200-500 nm. In some embodiments, the characteristic wavelength of the UV-coated fused silica plano-convex cylindrical lens is 245-440 nm.
  • the phase mask 1607 is disposed in front of the raw material 1608. After being irradiated with a laser beam, strip-shaped spots can be formed on the raw material 1608.
  • the phase mask 1607 is an ultraviolet irradiation 248nm characteristic wavelength ultra-bandwidth (for example, 1460-1600nm) phase mask.
  • the width of the strip-shaped light spot is, for example, 10 mm, 15 mm, 20 mm, 25 mm, etc.; the height is, for example, 28 ⁇ m, 32.4 ⁇ m, 40 ⁇ m, 50 ⁇ m, etc.
  • the motion drive controller 1612 is connected to and controls the motion driver 1611 to drive the fixation device 1610 to move, for example, translation and/or rotation.
  • the specially prepared raw materials are irradiated by the FBG irradiation equipment 1600.
  • the process of preparing the FBG sensor includes the following steps:
  • S16-1 Fix both ends of the raw material 1608 to the slide rail 1609 and the fixing device 1610 respectively.
  • the fixing device 1610 is fixedly connected to the motion driver 1611.
  • Fixing device 1610 may be a clamp.
  • the clamp may clamp and secure one end of the raw material 1608 .
  • the laser controller 1602 controls the laser 1603 to emit laser. After the laser passes through the above-mentioned beam correction devices 1604-1 and 1604-2, the slit diaphragm 1605, the ultraviolet coating lens 1606 and the phase mask 1607, Strip-shaped light spots are generated on the surface of the raw material 1608.
  • the motion drive controller 1612 controls the motion driver 1611 to drive the raw material 1608 to move. During the movement of the raw material 1608, the laser irradiates the raw material 1608 to form the FBG sensor.
  • the fixing device 1610 is fixedly connected to the motion driver 1611.
  • the motion drive controller 1612 controls the motion driver 1611 to drive the fixing device 1610 to move
  • the raw material 1608 also moves (translation, rotation, etc.) accordingly.
  • the strip-shaped spot formed by the laser through the phase mask 1607 is irradiated on the surface of the raw material 1608, so that the refractive index of the optical fiber core is periodically modulated.
  • Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other.
  • the input beam only experiences strong reflection at a specific wavelength determined by a certain phase matching condition, called the Bragg wavelength of the FBG, which ultimately forms the FBG sensor.
  • Figure 17 is a schematic diagram of a medical treatment device according to some embodiments of the present specification.
  • the medical treatment device 1700 may be a device that integrates various devices and components in the medical treatment system 100 (local or remote). As shown in the figure, the medical treatment device 1700 may include MRI equipment (not shown in the figure), LITT equipment (not shown in the figure), temperature measurement equipment (not shown in the figure), OCT equipment (not shown in the figure) ), control device 1710, interface platform line control module 1720, driving component 1730, probe group 1740, temperature feedback control unit 1750, laser dose control unit 1760, attenuator adjustment control unit 1770, attenuator adjustment unit 1780 and laser Power Attenuator 1790.
  • MRI equipment not shown in the figure
  • LITT equipment not shown in the figure
  • temperature measurement equipment not shown in the figure
  • OCT equipment not shown in the figure
  • the MRI equipment is used to image a specific area including a target object (for example, a cancer lesion) to generate an MRI image.
  • the MRI image may be a real-time MRI image or a non-real-time MRI image.
  • the MRI image may include a three-dimensional image or multiple two-dimensional images (eg, cross-sectional, coronal, and sagittal images), representing information (eg, position and size, etc.) of the target object in the three-dimensional space.
  • the information about the target object in the three-dimensional space provided by the MRI image can be used before treatment.
  • the LITT probe, the OCT probe and/or the temperature measurement element of the temperature measurement device of the probe set 1740 pass through the human tissue to reach the target.
  • the path at the object is planned (referred to as needle entry planning).
  • the information of the target object in the three-dimensional space provided by the MRI image can also be used in the treatment process to guide the LITT probe, OCT probe and/or temperature measurement element to enter the human tissue according to the planned path and reach the Target object (referred to as needle insertion guide).
  • the MRI image may be displayed on a terminal (eg, terminal 150).
  • a user such as a doctor, can perform needle insertion planning and needle insertion guidance of the LITT probe and/or temperature measurement element based on the MRI image through a terminal (for example, a touch screen, a mouse, a keyboard and other physical components on the terminal 150).
  • the system can also automatically perform needle insertion planning and needle insertion guidance for the LITT probe and/or temperature measurement element based on the MRI image.
  • the MRI equipment can also perform magnetic resonance thermography on a specific area including the target object to generate a thermal image.
  • the thermal image may be registered with the MRI image to simultaneously represent the anatomical structure information of the specific region containing the target object and the temperature change information of the corresponding location.
  • the LITT equipment is used to generate laser light and use the thermal effect of the laser to treat the target object.
  • the LITT device includes a laser, a LITT probe (eg, a LITT lateral ablation probe, a LITT circumferential ablation probe), and a channel (such as an optical fiber) and interface connecting the laser and the LITT probe.
  • the laser may include a tunable laser diode and/or a non-tunable laser diode.
  • the laser power of the tunable laser diode is tunable within a specific range, such as 0-500W, 0-250W, 0-50W, 0-10W, 1-8W, etc.
  • the laser power of the non-tunable laser diode is a specific value, for example, 1W, 3W, 5W, 8W, 10W, 12W, 15W, 20W, 30W, 60W, 100W, etc.
  • the laser has certain characteristic wavelengths, such as 840nm, 980nm, 1064nm, 1300nm, etc.
  • the temperature measuring device includes a temperature measuring element.
  • the temperature measurement element is used to measure the temperature of the target object or a specific position on its edge (for example, the position on the edge of the target object farthest from the LITT probe) to determine the temperature within the entire target object range. Tissue temperature to ensure treatment effect.
  • the distance between the LITT probe and the temperature measuring element is smaller than the size of the target object.
  • the edges of the target object are irregularly shaped.
  • the target object may be equivalent to a circle.
  • the smallest circumscribed circle of the target object may be determined as the equivalent circle of the target object.
  • the size of the target object is, for example, the diameter of the equivalent circle.
  • Temperature measurement elements can include thermocouples (such as K-type thermocouples), LITT photon temperature measurement probes, etc.
  • the temperature measurement element may be a LITT photon temperature measurement probe.
  • the LITT photon temperature measurement probe may include an FBG temperature measurement probe.
  • the FBG temperature measurement probe includes an optical fiber prepared using special raw materials, which is irradiated with ultraviolet light in a specific wavelength range (for example, 240-244nm, 244-248nm, 248-252nm, 252-256nm, etc.), causing the fiber core to refract The rate is periodically modulated. Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other.
  • the input beam only experiences strong reflection at a specific wavelength determined by certain phase matching conditions.
  • the reflected wavelength is called the Bragg wavelength of the FBG.
  • the phase matching condition called the Bragg condition, ultimately forms the FBG temperature measurement probe.
  • the FBG thermometric probe can be used for real-time monitoring of interstitial tissue at specific locations during laser ablation irradiation.
  • the OCT device Based on the light transmittance of biological structures, the OCT device detects the reflection, scattering and other signals of biological tissues, converts them into electrical signals, and generates OCT images.
  • the OCT image is a real-time OCT image, or a non-real-time OCT image.
  • the OCT device includes a light source, an OCT probe, an interference component, and an optical fiber and an interface connecting the components.
  • the light source uses a low-coherence light source to improve the longitudinal resolution of the imaging.
  • the OCT device can be a dual-mode OCT, and its light source can generate optical signals with two different parameters (bandwidth, central wavelength).
  • the dual-mode OCT uses an optical signal with a bandwidth of more than 160nm and a central wavelength of 840nm, and a sweep range of more than 100nm and a central wavelength of 1300nm.
  • Dual-mode OCT can provide pathological imaging with a resolution close to 1 ⁇ m and a depth of cm, so as to perform real-time pathological imaging of the actual morphology of ablation pathology and cell apoptosis, and then perform pathological evaluation.
  • the probe set 1740 includes the LITT photon ablation probe 1742 of the LITT device and the LITT photon thermometry probe 1744 of the temperature measurement device.
  • the above-mentioned LITT probe for example, LITT lateral ablation probe, LITT circumferential ablation probe
  • OCT probe can be integrated into one body to form an integrated probe integrating diagnosis and treatment (hereinafter referred to as integrated probe for short). probe).
  • LITT photon ablation probe 1742 may be the integrated probe.
  • the LITT photon temperature measurement probe 1744 and the LITT photon ablation probe 1742 are independent of each other (eg, have independent structures and are independently controlled).
  • the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 of the temperature measurement device are arranged at different positions relative to the target object.
  • the control device 1710 can be used to control one or more devices or components of the medical treatment device 1700 and perform corresponding operations.
  • the control device 1710 can generate corresponding instructions based on the device or component being controlled and the operations that need to be performed.
  • the instructions are conveyed to the corresponding device or component in the form of electrical signals, causing the device or component to perform corresponding operations.
  • the control device 1710 may include, for example, a microcontroller (MCU), a central processing unit (CPU), a programmable logic device (PLD), an application specific integrated circuit (ASIC), a single chip microcomputer (SCM), a system on a chip ( SoC) etc.
  • the control device 1710 may be an industrial computer.
  • the control device 1710 integrates an OCT control module 1711, a LITT control module 1713, an FBG control module 1715, a probe sensing module 1717, and a drive control module 1719.
  • the OCT control module 1711 is used to control OCT imaging of the target object.
  • the OCT control module 1711 can generate instructions to control the OCT device to emit and receive optical signals and/or set imaging parameters (eg, optical signal bandwidth, central wavelength of the optical signal, imaging time, image contrast, etc.).
  • the OCT control module 1711 can control the OCT device to emit a dual-mode OCT optical signal with a central wavelength of 840 nm exceeding a bandwidth of 160 nm, and a central wavelength of 1300 nm exceeding a 100 nm sweep range.
  • the optical signal is transmitted to the optical fiber slip ring device 1722, and after motion control and spatial coupling processing is performed on the optical fiber slip ring device 1722, it is finally transmitted to the OCT probe.
  • the OCT control module 1711 may also acquire the generated pathological diagnosis signal (eg, an optical signal carrying tissue pathological characteristics) to generate an OCT image.
  • the generated pathological diagnosis signal eg, an optical signal carrying tissue pathological characteristics
  • the LITT control module 1713 can control the LITT photon ablation probe 1742 to perform ablation treatment on the target object.
  • LITT control module 1713 integrates a laser controller.
  • the laser controller can control the laser of the LITT device (eg, the tunable laser diode and/or the non-tunable laser diode) to emit laser light to provide an ablation energy source for the entire LITT.
  • the LITT control module 1713 can control the laser to emit laser, and the emitted laser is transmitted to the LITT photon ablation probe 1742 through the optical path relay processing device 1724.
  • the LITT control module 1713 controls the laser of the LITT device to emit laser light of a specific wavelength (e.g., 980 nm or 1064 nm) with a specific power (e.g., at a power selected in the range of 1-8W), and the laser is transmitted to the optical path relay processing
  • the device 1724 performs a physical connection of the light path relay, and then transmits it to the LITT photon ablation probe 1742, which emits an ablation laser to ablate the target tumor tissue.
  • the FBG control module 1715 can control the temperature measuring element to obtain the temperature of a specific position on the edge of the target object.
  • the temperature measurement signal of the temperature measurement element (such as the heat source optical signal of the LITT photon temperature measurement probe 1744) can be transmitted through the optical path relay processing device 1724.
  • the FBG control module 1715 can control the LITT photon temperature probe 1744 to detect in real time a specific position on the edge of the target object (for example, the farthest edge of the tumor tissue, the farthest edge is ablated with LITT photons).
  • the probe 1742 is the temperature of the geometric distance measuring point, and transmits the temperature to the optical path relay processing device 1724, and finally to the FBG control module 1715.
  • the optical path relay processing device 1724 supports and ensures the optical path ring output to avoid conflict between the temperature measurement output optical path carrying temperature information and the temperature measurement incident optical path.
  • the FBG control module 1715 can modulate the spectral signal carrying the temperature scale benchmark, and convert the spectral signal into a specific temperature in the form of an electrical signal.
  • the probe sensing module 1717 can detect the real-time position of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 in real time by controlling the displacement controller 1726.
  • the probe sensing module 1717 may trigger changes in position signal feedback across the ergodic displacement controller 1726 by emitting an electrical signal, and the displacement controller 1726 may monitor and communicate with the dual-axis three-dimensional frame 1736 and the single-axis stereoscopic frame 1736 in real time, for example, through a displacement sensor.
  • the axis three-dimensional frame 1738 interacts to obtain the position information of the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 in a specific part of the patient (for example, within the skull or other organs of the human body) in real time.
  • the probe sensing module 1717 can also send control signals to the displacement controller 1726 in real time, issue displacement triggering instructions and receive position feedback processing signals.
  • the displacement triggering instruction is used to trigger the displacement controller 1726 to control the movement of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744.
  • the position feedback processing signal is used to determine and decide on the subsequent positions of the LITT photon ablation probe 1742 and/or the LITT photon temperature probe 1744 based on the real-time positions of the LITT photon ablation probe 1742 and/or the LITT photon temperature probe 1744. Movement (e.g., moving forward, adjusting direction, retracing, etc.).
  • At least one displacement sensor is mounted on the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 respectively. At least one displacement sensor on the biaxial three-dimensional frame 1736 is used to monitor the movement of the LITT photon ablation probe 1742. At least one displacement sensor on the uniaxial three-dimensional frame 1738 is used to monitor the movement of the LITT photon temperature probe 1744.
  • the displacement sensor may be, for example, a piezoelectric sensor, an inductive sensor, an eddy current sensor, etc.
  • the drive control module 1719 can send instructions through electrical signals to control the first drive device 1732 and/or the second drive device 1734 in the drive assembly 1730 to drive the movement of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744.
  • the first driving device 1732 also known as the ablation end driving device, is connected to and drives the LITT photon ablation probe 1742 to move (for example, translational, rotational motion) to achieve precise motion control of the LITT photon ablation probe 1742 with two degrees of freedom.
  • the second driving device 1734 is also called the temperature measurement end driving device, which is connected to and drives the movement (for example, translational movement) of the LITT photon temperature measurement probe 1744 to realize precise motion control of the LITT photon temperature measurement probe 1744 with one degree of freedom.
  • the movement of the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 requires mechanical clamping and power transmission support provided by the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 respectively.
  • the biaxial three-dimensional frame 1738 provides two different Power transmission with a single degree of freedom.
  • a single axis provides power transmission with a single degree of freedom.
  • the interface platform hub control module 1720 integrates mid-level or relay control of one or more components or elements of the medical treatment device 1700 .
  • the interface platform line control module 1720 integrates the above-mentioned optical fiber slip ring device 1722, optical path relay processing device 1724 and displacement controller 1726.
  • the interface platform hub control module 1720 includes a packaging box.
  • the optical fiber slip ring device 1722, the optical path relay processing device 1724, and the displacement controller 1726 are provided in the packaging box and connected to corresponding components or components through respective corresponding channels.
  • the optical fiber slip ring device 1722 is connected to the OCT probe through the OCT probe channel (optical fiber); the optical path relay processing device 1724 is connected to the LITT probe and the LITT photon measurement probe through the LITT ablation probe channel and the LITT temperature measurement probe channel respectively. Temperature probe 1744; displacement controller 1726 is connected to the displacement sensor through a displacement sensor cable channel.
  • the optical fiber slip ring device 1722 may be disposed on the propagation path of the optical signal generated by the OCT device (for example, at the rotary joint).
  • the optical fiber slip ring device is used to ensure uninterrupted transmission of optical signals.
  • a multi-channel optical fiber slip ring device can be used (such as a dual-channel optical fiber slip ring device to adapt to the above-mentioned two optical signals with different central wavelengths), also called a multi-mode optical fiber slip ring device.
  • the optical path relay processing device 1724 is used to process optical signals and ensure the continuity of optical signal propagation.
  • the laser light emitted by the laser of the LITT device is processed by the optical path relay processing device 1724 and then transmitted to the LITT probe.
  • the optical path relay processing device 1724 can adjust at least one parameter (eg, power, frequency, etc.) of the laser.
  • the optical path relay processing device 1724 can compensate for the attenuation of the laser so that it reaches a specific power, or perform attenuation processing on the laser so that its power meets the needs of treatment.
  • the optical path relay processing device 1724 supports and ensures the opposite transmission of the optical paths of the temperature measurement equipment to avoid the conflict between the temperature measurement output optical path carrying temperature information and the temperature measurement incident optical path, thereby interrupting or interfering with each other in optical signals.
  • the displacement controller 1726 may control the displacement of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 based on instructions from the probe sensing module 1717 .
  • the displacement controller 1726 can control the LITT photon ablation probe 1742 to pass through a specific part of the patient (for example, through the skull and into the skull) through the LITT ablation probe channel provided on the biaxial stereoscopic frame 1736 ), according to the needle insertion planning and needle insertion guidance of the LITT photon ablation probe 1742, the location of the target object is reached.
  • the displacement controller 1726 can control the LITT photon temperature measurement probe 1744 to pass through a specific part of the patient (for example, through the skull and into the skull) through the LITT temperature measurement probe channel fixedly provided on the single-axis three-dimensional frame 1738.
  • the needle insertion plan and needle insertion guide of the LITT photon temperature measurement probe 1744 the location of the target object is reached to measure the temperature of the edge of the target object or surrounding tissue located at a specific distance from the LITT photon temperature measurement probe 1744.
  • the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 are fixed to similar positions on specific parts of the patient (eg, head, chest, limbs, etc.).
  • the driving component 1730 is used to drive the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 to move, so that the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 reaches or moves away from a specific position (for example, , the location of the target object).
  • the movement of the LITT photon ablation probe 1742 may include translational movement and rotational movement.
  • the movement of the LITT photon thermometer probe 1744 may include translational movement.
  • the driving assembly 1730 includes a first driving device 1732 (also called an ablation end driving device) and a second driving device 1734 (also called a temperature measurement end driving device), which respectively control the LITT photon ablation probe 1742 and The LITT photon thermometer probe 1744 moves.
  • the first driving device 1732 is independent of the second driving device 1734 .
  • Each drive device may include a drive motor, cables, and motion control mechanisms.
  • the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 are physically connected to corresponding motion control mechanisms through respective connected cables. Through corresponding cables and motion control mechanisms, the force output by the corresponding drive motor can be transmitted to the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 to control their movement.
  • the first driving device 1732 is coupled to the LITT photon ablation probe 1742 and controls the translational movement and rotational movement of the LITT photon ablation probe 1742.
  • the first driving device 234 includes a first driving motor, a first translation cable, a first translation control mechanism, a first rotation cable, and a first rotation control mechanism.
  • the first translation control mechanism is used to control the translation movement of the LITT photon ablation probe 1742.
  • the first rotation control mechanism is used to control the rotation movement of the LITT photon ablation probe 1742.
  • the first translation cable and the first rotation cable are respectively connected to the first translation control mechanism and the first rotation control mechanism, and the first translation control mechanism and the first rotation control mechanism are connected to the LITT photon ablation
  • the probe 1742 controls the translational movement and rotational movement of the LITT photon ablation probe 1742 through the first translation cable and the first rotation cable respectively.
  • the first drive motor can drive the movement of the first translation cable and/or the first rotation cable as required, thereby controlling the translation and/or rotation movement of the LITT photon ablation probe 1742 to achieve the LITT photon ablation. Precise motion control of probe 1742 with two degrees of freedom.
  • the first translation control mechanism and the first rotation control mechanism may be provided on the biaxial three-dimensional frame 1736 .
  • the second driving device 1734 is coupled to the LITT photon temperature measurement probe 1744 and controls the translational movement of the LITT photon temperature measurement probe 1744.
  • the second driving device 1734 includes a second driving motor, a second translation cable, and a second translation control mechanism.
  • the second translation control mechanism is used to control the translation movement of the LITT photon temperature measurement probe 1744.
  • the second translation cable is connected to the second translation control mechanism, the second translation control mechanism is connected to the LITT photon temperature measurement probe 1744, and the LITT photon temperature measurement probe is controlled through the second translation cable. Translational movement of temperature probe 1744.
  • the second drive motor can drive the movement of the second translation cable as required, thereby controlling the translational movement of the LITT photon temperature measurement probe 1744 and achieving precise motion control of one degree of freedom of the LITT photon temperature measurement probe 1744 .
  • the second translation control mechanism may be provided on the single-axis three-dimensional frame 1738.
  • the above-mentioned cables are special silk threads with higher rigidity and lower elastic modulus, and can complete torque transmission in real time 1:1 to ensure the accuracy of driving the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 to move.
  • Biaxial stereoscopic frame 1736 and uniaxial stereoscopic frame 1738 may carry one or more components or elements of medical treatment device 1700 .
  • the components or elements carried by the biaxial three-dimensional frame 1736 include the LITT ablation probe channel of the LITT photon ablation probe 1742, a displacement sensor, a first motion control mechanism (such as the first translation control mechanism and the first Rotation control mechanism), etc.
  • the components or elements carried by the single-axis three-dimensional frame 1738 include the LITT temperature measurement probe channel of the LITT photon temperature measurement probe 1744, a displacement sensor, a second translation control mechanism, etc.
  • the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 can be fixed to a specific part of the patient (for example, two different positions of the skull), and maintain a stable connection with the specific part of the patient without relative displacement.
  • the components or elements carried by the biaxial three-dimensional frame 1736 and the single-axial three-dimensional frame 1738 can be fixedly connected to the biaxial three-dimensional frame 1736 and the single-axial three-dimensional frame 1738, respectively.
  • the temperature feedback control unit 1750 is used to monitor the temperature at a specific position on the edge of the target object measured by the LITT photon temperature probe 1744, and ensure that the measured temperature is within a preset temperature range.
  • the preset temperature range is set by the user, based on system default settings, etc.
  • the preset temperature range is 44 ⁇ 0.5°C, 44 ⁇ 1°C, 45 ⁇ 0.5°C, 45 ⁇ 1°C, 46 ⁇ 0.5°C, 46 ⁇ 1°C, 47 ⁇ 0.5°C, 47 ⁇ 1°C, 48 ⁇ 0.5°C, 48 ⁇ 1°C, etc.
  • the preset temperature range is 46 ⁇ 1°C.
  • the target object's tissue temperature is within this preset temperature range for better therapeutic effects.
  • the temperature feedback control unit 1750 is connected to the FBG control module 1715.
  • the FBG control module 1715 may transmit the temperature measured by the LITT photon temperature probe 1744 to the temperature feedback control unit 1750 as an electrical signal.
  • the transmission of the measured temperature may be real-time or intermittent (eg, periodic).
  • the temperature feedback control unit 1750 may determine the difference between the measured temperature and the preset temperature range (i.e. temperature difference), and output the difference value to the laser dose control unit 1760 to adjust the laser dose output by the LITT photon ablation probe 1742, so that the temperature measured by the LITT photon temperature measurement probe 1744 returns to the preset temperature within the range.
  • the laser dose control unit 1760 can determine the target laser output dose value (ie, the target laser dose value that needs to be output).
  • the laser dose control unit 1760 can be connected to the temperature feedback control unit 1750.
  • the laser dose control unit 1760 can obtain the value determined by the temperature feedback control unit 1750. temperature difference, and based on the temperature difference, the target laser output dose value is determined.
  • the target laser output dose value can be the total dose of laser within a specific time period, or it can be the dose value of laser at each time. Through the total dose of the laser during the time period or the dose value of the laser at each moment, the changing trend of the tissue temperature at the LITT photon temperature measurement probe 1744 can be determined, so that the temperature measured by the LITT photon temperature measurement probe 1744 returns to within the preset temperature range.
  • the above process of determining the changing trend of tissue temperature at the LITT photon thermometer probe 1744 can be determined based on a model or a specific algorithm.
  • the model may be, for example, a machine learning model.
  • Exemplary machine learning models may include neural network models (e.g., deep learning models), generative adversarial networks (GAN), deep belief networks (DBN), stacked autoencoders (SAE), logistic regression (LR) models, support vectors Machine (SVM) model, decision tree model, naive Bayes model, random forest model or restricted Boltzmann machine (RBM), gradient boosted decision tree (GBDT) model, LambdaMART model, adaptive enhancement model, hidden Martian Kov model, perceptron neural network model, Hopfield network model, etc.
  • neural network models e.g., deep learning models
  • GAN generative adversarial networks
  • DBN deep belief networks
  • SAE stacked autoencoders
  • LR logistic regression
  • SVM support vectors Machine
  • decision tree model
  • Exemplary deep learning models may include deep neural network (DNN) models, convolutional neural network (CNN) models, recurrent neural network (RNN) models, feature pyramid network (FPN) models, etc.
  • Exemplary CNN models may include V-Net models, U-Net models, FB-Net models, Link-Net models, etc., or any combination thereof.
  • the model can be trained through historical data (for example, historical laser dose and historical temperature difference), thereby generating a trained model to determine the target laser output dose value.
  • the attenuator adjustment control unit 1770 can be connected to and control the attenuator adjustment unit 1780 so that the laser power attenuator 1790 adjusts the power of the output laser.
  • laser power attenuator 1790 may be an SMA variable high power laser attenuator.
  • the SMA variable high-power laser attenuator is provided with a power adjustment nut. By adjusting the forward and reverse adjustment of the nut, the output laser power can be adjusted.
  • the attenuator adjustment control unit 1770 may determine the adjustment direction and adjustment amount of the adjustment nut (for example, the number of turns of the nut) based on the current laser output dose value and the target laser output dose value.
  • the temperature feedback control unit 1750, the laser dose control unit 1760 and/or the attenuator adjustment control unit 1770 can be integrated as a processing module, and the processing module operates independently with respect to the control device 1710 and is connected with the medical device 1710.
  • the various components or devices of treatment device 1700 are connected to each other.
  • the processing module may determine the target laser output dose value of the LITT device based on the difference between the measured temperature and the preset temperature range, so that the temperature measured by the temperature measuring element is within the preset temperature range.
  • the processing module may be or include, for example, a microcontroller (MCU), a central processing unit (CPU), a programmable logic device (PLD), an application specific integrated circuit (ASIC), a single chip microcomputer (SCM), a system on a chip (SoC) etc.
  • MCU microcontroller
  • CPU central processing unit
  • PLD programmable logic device
  • ASIC application specific integrated circuit
  • SCM single chip microcomputer
  • SoC system on a chip
  • the attenuator adjustment unit 1780 can be connected to and control the laser power attenuator 1790.
  • the attenuator adjustment unit 1780 can control the laser power attenuator 1790 to attenuate or gain the input laser power by a certain proportion based on the instructions generated by the attenuator adjustment control unit 1770 (for example, the adjustment direction and adjustment amount of the above-mentioned nut).
  • the laser power attenuator 1790 is an SMA variable high-power laser attenuator.
  • the attenuator adjustment unit 1780 can be, for example, an electric screw adjustment stepping element.
  • the electric screw adjustment stepping element can include a micro drive motor. Through the micro drive motor, the nut can be adjusted according to the determined adjustment direction and adjustment amount of the nut.
  • the laser power attenuator 1790 can adjust the current laser output dose value to the target laser output dose value by attenuating or gaining a certain proportion of the input laser power.
  • the laser power attenuator 1790 can attenuate the input laser power by, for example, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80% or 90%, or gain, for example, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80%, 90%, 100%, 120%, 150%, etc. (i.e. power attenuation/gain processing).
  • the laser power attenuator 1790 dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measuring element is always within the preset temperature range.
  • the laser power attenuator 1790 dynamically adjusts the current laser output dose value so that the temperature measurement element measures The obtained temperature is always within the preset temperature range. At this time, the laser power output by the laser of the LITT device is always the target laser output dose value.
  • the laser is transmitted to the LITT photon ablation probe 1742 through the optical path relay processing device 1724 to reach Adjust and adapt the laser ablation energy to the purpose.
  • the operation between the above-mentioned modules, units or components can be a dynamic adjustment process, through a back-and-forth cycle, so that the temperature measured by the LITT photon temperature measurement probe 1744 (for example, the temperature of the farthest edge of the target object) is always dynamically maintained at within the preset temperature range. Electrical connections are established between each unit, and the temperature control signal is transmitted in real time and stably in the form of an electrical signal. Combined with the accuracy of the LITT photon temperature measurement probe 1744 (more accurate than the previous MRTI temperature measurement), the temperature is increased. The precision of the control and the timeliness of the feedback adjustment ensure that the temperature at the farthest edge of the target object relative to the LITT photon ablation probe 1742 is always maintained within the preset temperature range, thus ensuring the treatment effect.
  • Figure 18 is a schematic diagram of a LITT photon temperature measurement probe according to some embodiments of the present specification.
  • the LITT photon temperature measurement probe 1805 is arranged in a probe sleeve, which is made of a specific material that is resistant to high temperatures and corrosion, such as polyetheretherketone (PEEK).
  • LITT photon temperature measurement probe 1805 can be an FBG temperature measurement probe (also known as FBG sensor).
  • the FBG temperature measurement probe includes an optical fiber prepared using special raw materials, which is irradiated with ultraviolet light in a specific wavelength range (for example, 240-244nm, 244-248nm, 248-252nm, 252-256nm, etc.).
  • the raw material for preparing the FBG temperature measurement probe can be fixed on a fixing device (for example, a clamp), and the fixing device is fixedly connected to the motion driver.
  • the laser controller controls the laser to emit laser, which passes through the beam correction device (for example, two oppositely arranged 248nm characteristic wavelength excimer laser 45° line mirrors), the slit diaphragm (for example, a 4.5mm width diaphragm) ), after UV coating lens (for example, 245-440nm characteristic wavelength UV coating fused silica plano-convex cylindrical lens) and phase mask (for example, UV irradiation 248nm characteristic wavelength 1460-1600nm ultra-bandwidth phase mask), after the raw material Strip-like spots appear on the surface.
  • the motion drive controller controls the motion driver to drive the raw material to move. During the movement of the raw material, the raw material is irradiated by the laser, thereby forming the FBG temperature measurement probe.
  • the drive motor 1810 may provide driving force to the single-axis stereotaxic frame via the drive cable 1815 (e.g., the second translation cable described above) that supports forward/retract translation motion.
  • 1820 e.g., the single-axis three-dimensional frame 1738 described above
  • a displacement sensor (not shown in the figure), installed on the single-axis three-dimensional frame 1820, can monitor the movement position of the LITT photon temperature measurement probe 1744.
  • the sensing signal of the displacement sensor is transmitted through the displacement sensor cable 1825.
  • the temperature sensing spectrum light signal measured by the LITT photon temperature measurement probe 1805 is sent to the temperature feedback control unit 1750 in real time through the LITT temperature measurement probe channel 1830.
  • the integrated component 1835 provides interface support for the portable connector mounted on the LITT temperature measurement probe channel 1830.
  • Figure 19 is a schematic diagram of a LITT photon ablation probe according to some embodiments of the present specification.
  • the LITT photon ablation probe may be a LITT photon lateral ablation probe 1910 or a LITT photon circumferential ablation probe 1920.
  • LITT photon lateral ablation probe 1910 may include an OCT probe 1912 and a LITT lateral ablation probe 1914.
  • LITT photon circumferential ablation probe 1920 may include an OCT probe 1922 and a LITT circumferential ablation probe 1924.
  • the LITT photon lateral ablation probe 1910 and the LITT photon circumferential ablation probe 1920 may each include a probe sleeve made of a specific material that is resistant to high temperatures and corrosion, such as polyetheretherketone (PEEK). )production.
  • PEEK polyetheretherketone
  • the LITT lateral ablation probe 1914 includes a probe body, a connection surface and a coating.
  • the connection surface is the connection interface between the body and the coating.
  • the probe body is cylindrical.
  • the probe body consists of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • the end (distal end) of the probe body has a certain inclination angle (that is, the end surface of the probe body forms a certain angle with the axis of the probe body, and the included angle is an acute angle).
  • the connection surface is formed by smoothing the end surface of the probe body.
  • the plating uses noble metal (eg, gold, silver, and platinum group metals) target plating.
  • the coating layer may be formed by magnetron sputtering coating on the surface of the connection surface.
  • the coating of the LITT lateral ablation probe 1914 may be replaced with a lens (eg, a sapphire lens).
  • the end (distal end) of the probe body can be a straight surface or have a certain inclination angle (that is, the end surface of the probe body is perpendicular to or at a certain angle with the axis of the probe body, and the included angle is an acute angle) ).
  • the connection surface and the lens are welded by arc welding or high-temperature melting of tungsten (such as tungsten wire), iridium (such as iridium wire) and other materials, and the tungsten wire or iridium wire is selected for the high-temperature melting of tungsten or iridium.
  • the fire polishing process is to fire polish the welded surface.
  • the LITT circumferential ablation probe 1924 may include a probe body.
  • the probe body consists of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • a tapered surface is set at the far end of the probe body (the end closest to the target object.
  • the diameter of the tapered surface gradually decreases from the initial diameter to the preset diameter.
  • the tapered surface is provided with grooves, for example, formed by optical machine engraving. Laser light directed to the LITT circumferential ablation probe can emerge from the groove.
  • the grooves are evenly (dispersed) distributed along the tapered surface in a certain pattern shape (for example, thread shape) and do not overlap with each other.
  • the distribution pattern of the grooves is a single thread shape (spiral shape), a multi-thread cross shape (for example, a double thread cross), a rhombus grid shape, a honeycomb shape, etc., or a combination thereof.
  • LITT lateral ablation probe 1914 and LITT circumferential ablation probe 1924 are the same as or respectively the LITT lateral ablation probes 700, 800 and LITT circumferential ablation probe 900 described in Figures 6-11. Similar, will not be repeated here.
  • a drive motor 1930 may provide drive force via a drive cable 1935 (e.g., the first translation cable described above) that supports forward/retract translational motion, and a drive cable 1935 that supports rotational motion.
  • a drive cable 1935 e.g., the first translation cable described above
  • the driving cable 1940 (for example, the above-mentioned first rotation cable) provides driving force to the biaxial stereoscopic frame 1945 (for example, the above-mentioned biaxial stereoscopic frame 1736), so that the LITT photon ablation probe (such as the LITT photon lateral ablation probe 1910 or LITT photon circumferential ablation probe 1920) to perform translational and rotational two-degree-of-freedom movements, thereby reaching a specific position of the target object (for example, the position shown in FIG. 20), and performing LITT irradiation on the target object. .
  • a displacement sensor (not shown in the figure) provided on the biaxial three-dimensional frame 1945 can monitor the movement position of the LITT photon ablation probe.
  • the sensing signal of the displacement sensor is transmitted through the displacement sensor cable channel 1950.
  • the LITT lateral ablation probe 1914 can receive the specific power transmitted by the LITT ablation probe channel 1955 (eg, 1-50W, 1-20W, 1-10W, 1-8W)
  • the high-power ablation laser is placed on the outside of the target object by placing the LITT photon lateral ablation probe 1910 and shoots towards the target object in a certain direction.
  • the OCT probe 1912 in the LITT photon lateral ablation probe 1910 can scan and image the ablation status or pathological diagnosis of the target object in real time, and transmit it back to the OCT control module 1711 through the OCT probe channel 1960 in real time.
  • the OCT probe channel 1960 and the LITT ablation probe channel 1955 are integrated (eg, mechanically coupled) through an integration component 1965 .
  • the LITT circumferential ablation probe 1924 can receive the specific power transmitted by the LITT ablation probe channel 1955 (eg, 1-50W, 1-20W, 1-10W, 1-8W)
  • the high-power ablation laser is diffused through the groove on the LITT circumferential ablation probe 1924 and directed towards the target object (for example, cancerous tissue).
  • the OCT probe 1922 in the LITT photon circumferential ablation probe 1920 can scan and image the ablation status or pathological diagnosis of the target object in real time, and transmit it back to the OCT control module 1711 through the OCT probe channel 1960 in real time.
  • Figure 20 is a schematic diagram of a LITT photon ablation probe and a LITT photon temperature measurement probe during treatment according to some embodiments of this specification.
  • the LITT photon temperature measurement probe 2010 and the LITT photon ablation probe can be placed in a preset Location.
  • the LITT photon temperature probe 2010 can obtain the temperature at a specific location on the edge of the target object.
  • the specific location may be the location furthest from the LITT photon ablation probe on the edge of the target object.
  • the distance between the LITT photon temperature measurement probe 2010 and the LITT photon ablation probe is smaller than the size of the target object.
  • the area within the edge of the target object may be, for example, irregularly shaped.
  • the target object may be equivalent to a circle.
  • the smallest circumscribed circle of the target object may be determined as the equivalent circle of the target object.
  • the size of the target object is, for example, the diameter of the equivalent circle.
  • the LITT photon ablation probe is a LITT photon circumferential ablation probe 2020
  • the LITT photon circumferential ablation probe 2020 (including the LITT circumferential ablation probe) is disposed on the
  • the LITT photon temperature measurement probe 2010 is disposed at the farthest position from the LITT photon circumferential ablation probe 2020 on the edge of the target object.
  • the distance between the LITT photon circumferential ablation probe 2020 and the LITT photon temperature measurement probe 2010 is set to L dispersion .
  • L dispersion is equal to or close to the equivalent radius of the target object.
  • the equivalent radius here is the radius of the smallest circumscribed circle of the edge of the target object.
  • the LITT photon circumferential ablation probe 2020 is set at the equivalent center, and the LITT photon temperature measurement probe 2010 is set at the target object
  • the edge is the farthest position from the LITT photon circumferential ablation probe 2020, thus ensuring that the temperature within the entire range of the target object is higher than the preset temperature range, thereby ensuring the accuracy of temperature measurement, and the temperature is from The equivalent center gradually decreases outward to ensure the therapeutic effect of the medical treatment device 1700.
  • the LITT photon lateral ablation probe 2030 (including the LITT lateral ablation probe) is disposed on one edge of the target object, so The LITT photon temperature measurement probe 2010 is disposed at the farthest position from the LITT photon lateral ablation probe 2030 on the edge of the opposite side of the target object.
  • the distance between the LITT photon lateral ablation probe 2030 and the LITT photon temperature measurement probe 2010 is set to L lateral direction .
  • L is laterally equal to or close to the equivalent diameter of the target object.
  • the equivalent diameter here is the diameter of the smallest circumscribed circle of the edge of the target object.
  • the photon temperature measurement probe 2010 is disposed on the edge of the opposite side of the target object at the farthest position from the LITT photon lateral ablation probe 2030, thus ensuring that the temperature within the entire range of the target object is higher than the predetermined temperature.
  • the temperature range is set to ensure the accuracy of temperature measurement, and the temperature gradually decreases from the side to the opposite side, thereby ensuring the treatment effect of the medical treatment device 1700.
  • the edge of the target object can be determined by using an image recognition or segmentation algorithm or model to process the MRI image containing the target object.
  • a typical image recognition or segmentation algorithm may include a convolution algorithm, that is, convolving image data with a specific operator to determine the edge contour in the image, where the specific operator may include a Roberts operator, a Sobel operator operator, Prewitt operator and zero-crossing Gaussian operator based on Laplacian operator.
  • the edge recognition algorithm may also include Canny detector, boosted edge learning algorithm (Boosted Edge Learning BEL) and other visual feature algorithms.
  • Boosted Edge Learning BEL boosted edge learning algorithm
  • Typical image recognition or segmentation models may include neural network models (e.g., deep learning models), generative adversarial networks (GAN), deep belief networks (DBN), stacked autoencoders (SAE), logistic regression (LR) models, support Vector machine (SVM) model, decision tree model, naive Bayes model, random forest model or restricted Boltzmann machine (RBM), gradient boosting decision tree (GBDT) model, Lambda MART model, adaptive enhancement model, Hidden Markov model, perceptron neural network model, Hopfield network model, etc. or any combination thereof.
  • the image recognition or segmentation model recognition is obtained by training historical images with target object edges in them as sample pairs.
  • the temperature feedback control unit 1750, the laser dose control unit 1760, the attenuator adjustment control unit 1770, the attenuator adjustment unit 1780 and the laser power controls the tissue temperature measured by the LITT photon thermometer probe 2010 to be in a preset temperature range (for example, 46 ⁇ 1°C).
  • the LITT circumferential ablation probe in the LITT photon circumferential ablation probe 2020 releases an ablation laser with a power of 1-8W and a characteristic wavelength of 1064nm to control the LITT photon temperature measurement probe 2010 always detects and based on the temperature feedback control unit 1750, laser dose control unit 1760, attenuator adjustment control unit 1770, attenuator adjustment unit 1780 and laser power attenuator 1790 feedback adjustment, the temperature at the location is within the preset temperature range.
  • the temperature of the tumor tissue adjacent to the LITT photon circumferential ablation probe 2020 will rise to nearly 100°C and rapidly coagulate and become necrotic, while the peripheral ring area will be an area where cells slowly undergo apoptosis for 48-72 hours or longer.
  • the laser light is continuously absorbed within the tissue, thereby generating continuous heat.
  • the higher temperature close to the LITT photon circumferential ablation probe 2020 causes cell membrane rupture and continued coagulation of proteins, resulting in continued instantaneous necrosis of the affected tissue.
  • the lower temperatures closer to the LITT photon thermoprobe 2010, which are causing the transition zone of apoptotic cells, can produce intermittent and ultimately death of immunogenic cells.
  • Beneficial effects that may be brought about by the embodiments of this specification include but are not limited to: (1) Temperature measurement by a remote thermocouple of the LITT probe that is more accurate than MRTI and/or temperature measurement by an FBG sensor, so that the temperature measurement performance of LITT can reach real-time Efficient feedback fully avoids damage caused by the distal end of the LITT probe and excessive tissue, reducing postoperative sequelae; (2)
  • the LITT ablation probe is used to carve cones and bevel carving processes to successfully create localized speckles that are smaller than the original ones.
  • the temperature feedback control unit 1750 laser dose control unit 1760, attenuator adjustment control unit 1770 (the three can be integrated into a processing module), attenuator adjustment unit 1780.
  • the laser power attenuator 1790 dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measurement element is always within the preset temperature range, combined with the LITT photon temperature measurement probe that is more accurate than MRTI.
  • Treatment efficiency and success rate of device 1700 (9) Combined with the position setting of LITT photon circumferential ablation probe/LITT photon lateral ablation probe and LITT photon temperature measurement probe, combined with LITT photon temperature measurement that is more accurate than MRTI probe, thus ensuring that the temperature within the entire range of the target object is higher than the preset temperature range, thereby ensuring the accuracy of temperature measurement, and the temperature gradually decreases outward from the equivalent center, thereby ensuring that the medical treatment device 1700 healing effect.
  • numbers are used to describe the quantities of components and properties. It should be understood that such numbers used to describe the embodiments are modified by the modifiers "about”, “approximately” or “substantially” in some examples. Grooming. Unless otherwise stated, “about,” “approximately,” or “substantially” means that the stated number is allowed to vary by ⁇ 20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximations that may vary depending on the desired features of the individual embodiment. In some embodiments, numerical parameters should account for the specified number of significant digits and use general digit preservation methods. Although the numerical ranges and parameters used to identify the breadth of ranges in some embodiments of this specification are approximations, in specific embodiments, such numerical values are set as accurately as is feasible.

Abstract

Provided is a medical treatment device. The medical treatment device comprises a magnetic resonance imaging (MRI) apparatus, which is configured to image a specific region comprising a target object to generate a magnetic resonance image; a laser interstitial thermotherapy (LITT) apparatus, which comprises: an LITT probe, which, on the basis of the magnetic resonance image, approaches the target object and treats the target object by emitting laser; and a temperature measuring element, which is integrated with the LITT probe into an integrated probe and is configured to acquire the temperature of the target object.

Description

一种医学治疗装置及治疗探针Medical treatment device and treatment probe 技术领域Technical field
本发明涉及医学诊断治疗领域，特别涉及一种医学治疗装置及治疗探针。The present invention relates to the field of medical diagnosis and treatment, and in particular to a medical treatment device and a treatment probe.
背景技术Background technique
激光间质热疗(LITT)是一种使用激光的热效应破坏靶组织的治疗方式，也是目前最新的治疗脑部肿瘤的微创手术。其基本原理为利用神经外科中立体定向的方式，将一根带有冷却循环套管的光纤探头介入患者脑部病灶，治疗时将激光通过光纤到达探针，从而加热探针周围的病灶组织，实现消融的目的。同时，还通过磁共振引导(MRg)LITT过程，以确定消融目标。Laser interstitial thermotherapy (LITT) is a treatment method that uses the thermal effect of laser to destroy target tissue. It is also the latest minimally invasive surgery for the treatment of brain tumors. The basic principle is to use the stereotactic method in neurosurgery to insert an optical fiber probe with a cooling circulation sleeve into the patient's brain lesion. During treatment, the laser reaches the probe through the optical fiber, thereby heating the lesion tissue around the probe. achieve the purpose of ablation. At the same time, a magnetic resonance-guided (MRg) LITT process is also used to determine the ablation target.
目前的LITT系统，存在如下问题：(1)以磁共振热成像(MRTI)对LITT探针系统远端及周围消融目标灶进行测温，由于距离目标灶点距离较远导致MRTI测温难以保障实时温度控制和检测的精准性，时常需要额外的算法预估来进行非实时的补偿，通常具有迟滞的算法理论主观性，而导致周围健康组织热损伤难以量化避免；(2)高功率LITT的扩散施源器作为LITT探针最核心的结构在工艺制造上不够均匀，物理散射单元过于集中，导致矢量光能在辐照周围目标凝固甚至消融病理组织时不够彻底，时常导致部分区域已经过度治疗，但有的区域治疗则尚未完成，导致治疗不彻底，且容易导致过度区域碳化，术后难于获得良好的愈后疗效；(3)高功率LITT的术中缺乏一种可以实时准确评估消融疗效的机制，导致消融时仅仅只能依靠MRI来进行1mm级的宏观成像进行粗略的切缘判断，更多需要患者出院后，结合术后的数月MRI回访，才能评估肿瘤的复发或者残余，这导致了一旦复发，患者是否还有资格接受二次手术面临巨大风险；(4)高功率LITT的制动方式多为医生手动制动，回撤精度难以控制，旋转性能难以实现，对需要兼容不规则肿瘤的目标病灶外侧向消融无法兼容，导致对于高度不规则肿瘤，以及健康神经功能区或敏感消融临近部位处置难度巨大，延误患者的手术治疗和造成严重术后后遗症。The current LITT system has the following problems: (1) Magnetic resonance thermal imaging (MRTI) is used to measure the temperature of the distal and surrounding ablation target lesions of the LITT probe system. Due to the long distance from the target lesion, MRTI temperature measurement is difficult to guarantee. The accuracy of real-time temperature control and detection often requires additional algorithm estimation for non-real-time compensation, which usually has hysteretic subjectivity in algorithm theory, making it difficult to quantify and avoid thermal damage to surrounding healthy tissue; (2) High-power LITT As the core structure of the LITT probe, the diffusion applicator is not uniform enough in manufacturing process, and the physical scattering units are too concentrated. As a result, the vector light energy is not thorough enough when irradiating surrounding targets to coagulate or even ablate pathological tissues, often resulting in over-treatment of some areas. , but the treatment in some areas has not been completed, resulting in incomplete treatment and easy to cause excessive regional carbonization, making it difficult to obtain good postoperative curative effect; (3) There is no method of high-power LITT that can accurately evaluate the ablation efficacy in real time. Due to this mechanism, ablation can only rely on MRI to perform 1mm-level macroscopic imaging for rough judgment of the resection margin. It is more necessary for patients to be discharged from the hospital and combined with MRI follow-up visits several months after surgery to evaluate the recurrence or residual of the tumor. This As a result, in the event of recurrence, whether the patient is still eligible for a second operation faces huge risks; (4) The braking method of high-power LITT is mostly manual braking by doctors, which makes it difficult to control the retraction accuracy, difficult to achieve rotation performance, and is not compatible with the needs. Lateral ablation of target lesions of regular tumors is incompatible, which makes it difficult to treat highly irregular tumors, healthy nerve functional areas or sensitive ablation adjacent areas, delaying the patient's surgical treatment and causing serious postoperative sequelae.
因此，亟需一种新的LITT设备，以解决上述问题，有效实现“查(成像诊断)打(消融治疗)一体”，增强治疗的准确性和成功率。Therefore, a new LITT device is urgently needed to solve the above problems, effectively achieve "inspection (imaging diagnosis) and treatment (ablation treatment) in one", and enhance the accuracy and success rate of treatment.
发明内容Contents of the invention
一种医学治疗装置及治疗探针。所述医学治疗装置包括：磁共振成像(MRI)设备，被配置为对包括目标对象的特定区域进行成像，生成磁共振图像；激光间质热疗(LITT)设备，包括：LITT探针，基于所述磁共振图像，所述LITT探针靠近所述目标对象，并通过发射激光对所述目标对象进行治疗；和测温元件，与所述LITT探针集成为集成探针，所述测温元件被配置为获取所述目标对象的温度。A medical treatment device and treatment probe. The medical treatment device includes: a magnetic resonance imaging (MRI) device configured to image a specific area including a target object and generate a magnetic resonance image; a laser interstitial thermotherapy (LITT) device including: a LITT probe based on In the magnetic resonance image, the LITT probe is close to the target object and treats the target object by emitting laser; and a temperature measurement element is integrated with the LITT probe into an integrated probe, and the temperature measurement element is The element is configured to obtain the temperature of the target object.
在一些实施例中，所述测温元件包括K型热电偶。In some embodiments, the temperature measuring element includes a K-type thermocouple.
在一些实施例中，所述K型热电偶靠近所述目标对象，实时采集所述目标对象的温度变化。In some embodiments, the K-type thermocouple is close to the target object to collect temperature changes of the target object in real time.
在一些实施例中，所述测温元件包括光纤布拉格光栅(FBG)传感器。In some embodiments, the temperature measurement element includes a fiber Bragg grating (FBG) sensor.
在一些实施例中，制备所述FBG传感器的原材料需满足：材料截止波长≤1280nm，1310nm时最大衰减标准取样≤0.35dB/km，1625nm时最大衰减标准取样≤0.23dB/km，1310nm时光纤模场直径(MFD)模式场外径＝9.2±0.4μm，1550nm时MFD模式场外径＝10.4±0.5μm，1550nm时色散≤18ps/(nm.km)，1625nm时色散≤22ps/(nm.km)，1310nm和1550nm时点不连续性≤0.05dB，1310nm时有效折射率群1.467，1550nm时有效折射率群1.4677，1310nm时瑞丽背向散射系数-77dB，以及1550nm时瑞丽背向散射系数-82dB。In some embodiments, the raw materials for preparing the FBG sensor need to meet the following requirements: material cut-off wavelength ≤ 1280nm, maximum attenuation standard sampling at 1310nm ≤ 0.35dB/km, maximum attenuation standard sampling at 1625nm ≤ 0.23dB/km, fiber mode at 1310nm Field diameter (MFD) mode field outer diameter=9.2±0.4μm, MFD mode field outer diameter=10.4±0.5μm at 1550nm, dispersion ≤18ps/(nm.km) at 1550nm, dispersion ≤22ps/(nm.km) at 1625nm ), point discontinuity at 1310nm and 1550nm ≤ 0.05dB, effective refractive index group at 1310nm 1.467, effective refractive index group at 1550nm 1.4677, Ruili backscattering coefficient at 1310nm -77dB, and Ruili backscattering coefficient at 1550nm -82dB .
在一些实施例中，所述FBG传感器靠近所述目标对象，确定所述目标对象的温度变化，其中，所述目标对象 的温度变化是基于获取的FBG的热敏性FBG的热敏性S FSG，通过对布拉格波长漂移Δλ S与温度变化ΔT之间的关系进行校准而确定的。 In some embodiments, the FBG sensor is close to the target object and determines a temperature change of the target object, wherein the temperature change of the target object is based on the acquired thermal sensitivity of the FBG and the thermal sensitivity of the FBG, S FSG , by The relationship between the wavelength drift Δλ S and the temperature change ΔT is determined by calibration.
在一些实施例中，对布拉格波长漂移Δλ S与温度变化ΔT之间的关系是通过将所述FBG传感器置于温度控制器内，所述温度控制器的温度间歇性变化，同时，由放大自发辐射(ASE)激光器通过环形器，到达所述FBG传感器，所述FBG传感器的反射信号通过所述环形器进入电信光谱分析仪，所述电信光谱分析仪监测所述FBG传感器的反射光谱从而确定的。 In some embodiments, the relationship between the Bragg wavelength shift Δλ S and the temperature change ΔT is obtained by placing the FBG sensor in a temperature controller, the temperature of the temperature controller changes intermittently, and at the same time, the amplified spontaneous The radiation (ASE) laser passes through the circulator and reaches the FBG sensor. The reflection signal of the FBG sensor enters the telecommunications spectrum analyzer through the circulator. The telecommunications spectrum analyzer monitors the reflection spectrum of the FBG sensor to determine .
在一些实施例中，所述医学治疗装置进一步包括光学相干断层成像(OCT)设备，被配置为对所述目标对象进行成像，生成OCT图像。In some embodiments, the medical treatment device further includes an optical coherence tomography (OCT) device configured to image the target object and generate an OCT image.
在一些实施例中，所述OCT设备包括OCT探针，所述OCT探针向所述目标对象发射光信号，用以对治疗过程中的所述目标对象进行成像，所述OCT探针发射的光信号具有两种不同的中央波长。In some embodiments, the OCT device includes an OCT probe that emits a light signal to the target object to image the target object during treatment, and the OCT probe emits a light signal. The optical signal has two different central wavelengths.
在一些实施例中，所述OCT探针与所述LITT探针和所述测温元件集成于所述集成探针。In some embodiments, the OCT probe, the LITT probe and the temperature measurement element are integrated into the integrated probe.
在一些实施例中，所述医学治疗装置进一步包括：驱动装置，包括：平移线缆和旋转线缆，以及平移控制机构和旋转控制机构，其中，所述平移线缆和旋转线缆分别连接于所述平移控制机构和旋转控制机构，所述平移控制机构和旋转控制机构连接于所述LITT探针，通过所述平移线缆和所述旋转线缆，分别控制所述LITT探针的平移运动和旋转运动。In some embodiments, the medical treatment device further includes: a driving device including: a translation cable and a rotation cable, and a translation control mechanism and a rotation control mechanism, wherein the translation cable and the rotation cable are respectively connected to The translation control mechanism and the rotation control mechanism, which are connected to the LITT probe, control the translation movement of the LITT probe respectively through the translation cable and the rotation cable. and rotational motion.
在一些实施例中，所述平移控制机构包括蜗轮蜗杆组件和同步带传动组件，所述旋转控制机构包括同步带传动组件。In some embodiments, the translation control mechanism includes a worm gear assembly and a timing belt transmission assembly, and the rotation control mechanism includes a timing belt transmission assembly.
在一些实施例中，所述LITT探针为LITT侧向消融探针或LITT周向消融探针。In some embodiments, the LITT probe is a LITT lateral ablation probe or a LITT circumferential ablation probe.
在一些实施例中，所述LITT侧向消融探针包括：探针主体；和覆盖于所述探针主体端面的镀层，其中，所述探针主体的端面与探针主体的轴线呈第一夹角，所述探针主体包括针芯和位于针芯外周的硬质包层，所述镀层为贵金属靶材镀层。In some embodiments, the LITT lateral ablation probe includes: a probe body; and a coating covering the end surface of the probe body, wherein the end surface of the probe body and the axis of the probe body form a first angle, the probe body includes a needle core and a hard cladding located on the outer periphery of the needle core, and the coating is a noble metal target coating.
在一些实施例中，所述镀层为双层结构，靠近所述探针主体端面的层为纯银，远离所述探针主体端面的层为一氧化硅。In some embodiments, the plating layer has a double-layer structure, the layer close to the end surface of the probe body is pure silver, and the layer far away from the end surface of the probe body is silicon monoxide.
在一些实施例中，所述LITT侧向消融探针是通过对所述探针主体的端面进行光洁化，然后对光洁化后的端面通过磁控溅射镀膜覆盖所述镀层而得到的。In some embodiments, the LITT lateral ablation probe is obtained by smoothing the end surface of the probe body, and then covering the smoothed end surface with the coating by magnetron sputtering coating.
在一些实施例中，所述LITT侧向消融探针包括：探针主体；和连接于所述探针主体端面的透镜，其中，所述探针主体的端面与探针主体的轴线垂直，所述透镜具有第一顶角，所述探针主体包括针芯和位于针芯外周的硬质包层，所述透镜为蓝宝石透镜。In some embodiments, the LITT lateral ablation probe includes: a probe body; and a lens connected to an end surface of the probe body, wherein the end surface of the probe body is perpendicular to the axis of the probe body, so The lens has a first vertex angle, the probe body includes a needle core and a hard cladding located on the outer periphery of the needle core, and the lens is a sapphire lens.
在一些实施例中，所述透镜为斜切的圆柱形透镜，或斜切的半球形或半椭球形透镜。In some embodiments, the lens is a beveled cylindrical lens, or a beveled hemispherical or hemispherical lens.
在一些实施例中，所述LITT侧向消融探针是通过对所述探针主体的端面进行光洁化，然后将所述探针主体和所述透镜进行熔接，并对熔接面进行火抛光而得到的。In some embodiments, the LITT lateral ablation probe is produced by smoothing the end surface of the probe body, welding the probe body and the lens, and performing fire polishing on the welded surface. owned.
在一些实施例中，所述LITT周向消融探针包括：探针主体，所述探针主体包括锥形面，所述锥形面上设置有凹槽，所述凹槽呈花纹状均匀分布于所述锥形面，其中，所述LITT探针产生的激光从所述凹槽处出射。In some embodiments, the LITT circumferential ablation probe includes: a probe body, the probe body includes a conical surface, the conical surface is provided with grooves, the grooves are evenly distributed on the conical surface in a pattern, wherein the laser generated by the LITT probe is emitted from the grooves.
在一些实施例中，所述锥形面的直径由初始直径逐渐缩小至预设直径，所述初始直径为630μm，所述预设直径为100μm。In some embodiments, the diameter of the tapered surface gradually decreases from an initial diameter to a preset diameter, where the initial diameter is 630 μm, and the preset diameter is 100 μm.
在一些实施例中，所述花纹包括单螺纹形状，交叉螺纹形状或菱形网格形状或其组合。In some embodiments, the pattern includes a single thread shape, a cross-thread shape or a diamond grid shape or a combination thereof.
在一些实施例中，所述锥形面通过执行如下操作形成：将待雕锥工件的两端分别固定于滑轨和固定器件；激光器控制器控制激光器发射激光，所述激光的功率为30W，波长为10600nm，所述激光经激光功率衰减器衰减至6.6到11.2W，衰减处理后的激光经衍射分束透镜单元分为两束激光，所述两束激光功率相等，所述两束激光经过聚焦透镜单元聚焦至待雕锥工件表面；以及运动驱动控制器控制运动驱动器，驱动所述待雕锥工件运动。In some embodiments, the tapered surface is formed by performing the following operations: fixing both ends of the tapered workpiece to be carved on the slide rail and the fixing device respectively; the laser controller controls the laser to emit laser, and the power of the laser is 30W, The wavelength is 10600nm. The laser is attenuated to 6.6 to 11.2W by the laser power attenuator. The attenuated laser is divided into two laser beams through the diffraction beam splitting lens unit. The power of the two laser beams is equal. The two laser beams pass through The focusing lens unit focuses on the surface of the workpiece to be carved into a cone; and the motion drive controller controls the motion driver to drive the movement of the workpiece to be carved into a cone.
在一些实施例中，所述呈花纹状均匀分布于所述锥形面的凹槽通过执行如下操作形成：将待雕花工件的两端分别固定于滑轨和固定器件；激光器控制器控制激光器发射激光，所述激光的功率为30W，波长为10600nm，所述激光经透镜组，聚焦至所述待雕花工件表面，所述透镜组包括第一凹透镜、第一凸透镜和第二凹透镜，所述第一凹透镜和第一凸透镜用于将激光束的直径扩展到第一直径，第二凹透镜用于将第一直径的激光束聚焦至待雕花工件表面，形成光斑，所述光斑直径为45μm；以及运动驱动控制器控制运动驱动器，驱动所述待雕花工件运动。In some embodiments, the pattern-like grooves evenly distributed on the tapered surface are formed by performing the following operations: fixing both ends of the workpiece to be carved to the slide rail and the fixing device respectively; the laser controller controls the laser emission Laser, the power of the laser is 30W, the wavelength is 10600nm, the laser is focused to the surface of the workpiece to be carved through a lens group, the lens group includes a first concave lens, a first convex lens and a second concave lens, the third concave lens A concave lens and a first convex lens are used to expand the diameter of the laser beam to a first diameter, and the second concave lens is used to focus the laser beam of the first diameter onto the surface of the workpiece to be engraved to form a light spot, the diameter of the light spot is 45 μm; and movement The drive controller controls the motion driver to drive the movement of the workpiece to be carved.
在一些实施例中，所述LITT周向消融探针发出的激光的空间强度分布通过如下方式获得：获取激光测量传感器输出的信号，生成所述LITT周向消融探针发出的激光的特定方位的极性强度，其中，所述LITT周向消融探针连接发射激光波长为632.8nm的氦氖激光器，所述激光测量传感器与所述LITT周向消融探针之间设置有狭缝光阑，所述狭缝光阑的狭缝尺寸为0.3mm；以及运动驱动控制器控制运动驱动器，以驱动所述光阑及激光测量传感器沿所述LITT周向消融探针的锥形面作周向和轴向运动，以所述获得LITT周向消融探针发出的激光的空间强度分布，其中，所述光阑与所述激光测量传感器固定连接于所述运动驱动器。In some embodiments, the spatial intensity distribution of the laser emitted by the LITT circumferential ablation probe is obtained by obtaining the signal output by the laser measurement sensor and generating a specific orientation of the laser emitted by the LITT circumferential ablation probe. Polarity intensity, wherein the LITT circumferential ablation probe is connected to a helium-neon laser with a laser wavelength of 632.8nm, and a slit diaphragm is provided between the laser measurement sensor and the LITT circumferential ablation probe, so The slit size of the slit diaphragm is 0.3mm; and the motion drive controller controls the motion driver to drive the diaphragm and the laser measurement sensor to perform circumferential and axial movements along the tapered surface of the LITT circumferential ablation probe. to obtain the spatial intensity distribution of the laser light emitted by the LITT circumferential ablation probe, wherein the aperture and the laser measurement sensor are fixedly connected to the motion driver.
本说明书另一个方面提供一种激光间质热疗(LITT)侧向消融探针，用于LITT设备，其特征在于，所述LITT侧向消融探针包括探针主体；和覆盖于所述探针主体端面的镀层，其中，所述探针主体的端面与探针主体的轴线呈第一夹角，所述探针主体包括针芯和位于针芯外周的硬质包层，所述针芯由纯二氧化硅材料制成，所述硬质包层由技术增强型包层二氧化硅(TECS)材料制成，所述镀层为贵金属靶材镀层。Another aspect of the present specification provides a laser interstitial thermal therapy (LITT) lateral ablation probe for use in a LITT device, characterized in that the LITT lateral ablation probe comprises a probe body; and a coating covering the end face of the probe body, wherein the end face of the probe body forms a first angle with the axis of the probe body, the probe body comprises a needle core and a hard cladding located on the outer periphery of the needle core, the needle core is made of pure silica material, the hard cladding is made of technology enhanced cladding silica (TECS) material, and the coating is a precious metal target coating.
在一些实施例中，所述镀层为双层结构，靠近所述探针主体端面的层为纯银，远离所述探针主体端面的层为一氧化硅。In some embodiments, the plating layer has a double-layer structure, the layer close to the end surface of the probe body is pure silver, and the layer far away from the end surface of the probe body is silicon monoxide.
在一些实施例中，所述靠近所述探针主体端面的层的厚度为100nm，远离所述探针主体端面的层的厚度为150nm，所述镀层与所述探针主体的轴线呈第二夹角为，所述第二夹角为47°。In some embodiments, the thickness of the layer close to the end face of the probe body is 100 nm, and the thickness of the layer far away from the end face of the probe body is 150 nm, and the plating layer and the axis of the probe body are at a second second angle. The included angle is, and the second included angle is 47°.
在一些实施例中，所述LITT侧向消融探针是通过对所述探针主体的端面进行光洁化，然后对光洁化后的端面通过磁控溅射镀膜覆盖所述镀层而得到的。In some embodiments, the LITT lateral ablation probe is obtained by smoothing the end surface of the probe body, and then covering the smoothed end surface with the coating by magnetron sputtering coating.
本说明书又一个方面提供一种激光间质热疗(LITT)侧向消融探针，用于LITT设备，其特征在于，所述LITT侧向消融探针包括：探针主体；和连接于所述探针主体端面的透镜，其中，所述探针主体的端面与探针主体的轴线垂直，所述透镜具有第一顶角，所述探针主体包括针芯和位于针芯外周的硬质包层，所述针芯由纯二氧化硅材料制成，所述硬质包层由TECS材料制成，所述透镜为蓝宝石透镜。Another aspect of this specification provides a laser interstitial thermotherapy (LITT) lateral ablation probe for LITT equipment, characterized in that the LITT lateral ablation probe includes: a probe body; and a probe connected to the A lens on the end face of the probe body, wherein the end face of the probe body is perpendicular to the axis of the probe body, the lens has a first vertex angle, the probe body includes a needle core and a hard package located on the outer periphery of the needle core layer, the needle core is made of pure silicon dioxide material, the hard cladding is made of TECS material, and the lens is a sapphire lens.
在一些实施例中，所述透镜为斜切的圆柱形透镜，或斜切的半球形或半椭球形透镜。In some embodiments, the lens is a beveled cylindrical lens, or a beveled hemispherical or semi-ellipsoidal lens.
在一些实施例中，所述LITT侧向消融探针是通过对所述探针主体的端面进行光洁化，然后将所述探针主体和所述透镜进行熔接，并对熔接面进行火抛光而得到的。In some embodiments, the LITT lateral ablation probe is produced by smoothing the end surface of the probe body, welding the probe body and the lens, and performing fire polishing on the welded surface. owned.
本说明书又一个方面提供一种激光间质热疗(LITT)周向消融探针，用于LITT设备，其特征在于，所述LITT探针周向消融包括：探针主体，所述探针主体包括锥形面，所述锥形面上设置有凹槽，所述凹槽呈花纹状均匀分布于所述锥形面，其中，所述LITT探针产生的激光从所述凹槽处出射。Another aspect of this specification provides a laser interstitial thermotherapy (LITT) circumferential ablation probe for LITT equipment, characterized in that the LITT probe circumferential ablation includes: a probe body, and the probe body It includes a tapered surface, and grooves are provided on the tapered surface. The grooves are evenly distributed on the tapered surface in a pattern, and the laser light generated by the LITT probe is emitted from the grooves.
在一些实施例中，所述锥形面的直径由初始直径逐渐缩小至预设直径，所述初始直径为630μm，所述预设直径为100μm。In some embodiments, the diameter of the tapered surface gradually decreases from an initial diameter to a preset diameter, where the initial diameter is 630 μm, and the preset diameter is 100 μm.
在一些实施例中，所述花纹包括单螺纹形状，交叉螺纹形状或菱形网格形状或其组合。In some embodiments, the pattern includes a single thread shape, a cross-thread shape or a diamond grid shape or a combination thereof.
在一些实施例中，所述锥形面通过执行如下操作形成：将待雕锥工件的两端分别固定于滑轨和固定器件；激光器控制器控制激光器发射激光，所述激光的功率为30W，波长为10600nm，所述激光经激光功率衰减器衰减至6.6到11.2W，衰减处理后的激光经衍射分束透镜单元分为两束激光，所述两束激光功率相等，所述两束激光经过聚焦透镜单元聚焦至待雕锥工件表面；以及运动驱动控制器控制运动驱动器，驱动所述待雕锥工件运动。In some embodiments, the tapered surface is formed by performing the following operations: fixing both ends of the tapered workpiece to be carved on the slide rail and the fixing device respectively; the laser controller controls the laser to emit laser, and the power of the laser is 30W, The wavelength is 10600nm. The laser is attenuated to 6.6 to 11.2W by the laser power attenuator. The attenuated laser is divided into two laser beams through the diffraction beam splitting lens unit. The power of the two laser beams is equal. The two laser beams pass through The focusing lens unit focuses on the surface of the workpiece to be carved into a cone; and the motion drive controller controls the motion driver to drive the movement of the workpiece to be carved into a cone.
在一些实施例中，所述呈花纹状均匀分布于所述锥形面的凹槽通过执行如下操作形成：将待雕花工件的两端分别固定于滑轨和固定器件；激光器控制器控制激光器发射激光，所述激光的功率为30W，波长为10600nm，所述激光经透镜组，聚焦至所述待雕花工件表面，所述透镜组包括第一凹透镜、第一凸透镜和第二凹透镜，所述第 一凹透镜和第一凸透镜用于将激光束的直径扩展到第一直径，第二凹透镜用于将第一直径的激光束聚焦至待雕花工件表面，形成光斑，所述光斑直径为45μm；以及运动驱动控制器控制运动驱动器，驱动所述待雕花工件运动。In some embodiments, the grooves uniformly distributed on the conical surface in a pattern are formed by performing the following operations: fixing the two ends of the workpiece to be carved to a slide rail and a fixing device respectively; a laser controller controls the laser to emit a laser, the power of the laser is 30W, the wavelength is 10600nm, the laser is focused onto the surface of the workpiece to be carved through a lens group, the lens group includes a first concave lens, a first convex lens and a second concave lens, the first concave lens and the first convex lens are used to expand the diameter of the laser beam to a first diameter, the second concave lens is used to focus the laser beam of the first diameter onto the surface of the workpiece to be carved to form a light spot, the diameter of the light spot is 45μm; and a motion drive controller controls the motion driver to drive the workpiece to be carved to move.
在一些实施例中，所述LITT周向消融探针发出的激光的空间强度分布通过如下方式获得：获取激光测量传感器输出的信号，生成所述LITT周向消融探针发出的激光的特定方位的极性强度，其中，所述LITT周向消融探针连接发射激光波长为632.8nm的氦氖激光器，所述激光测量传感器与所述LITT周向消融探针之间设置有狭缝光阑，所述狭缝光阑的狭缝尺寸为0.3mm；以及运动驱动控制器控制运动驱动器，以驱动所述光阑及激光测量传感器沿所述LITT周向消融探针的锥形面作周向和轴向运动，以所述获得LITT周向消融探针发出的激光的空间强度分布，其中，所述光阑与所述激光测量传感器固定连接于所述运动驱动器。In some embodiments, the spatial intensity distribution of the laser emitted by the LITT circumferential ablation probe is obtained by obtaining the signal output by the laser measurement sensor and generating a specific orientation of the laser emitted by the LITT circumferential ablation probe. Polarity intensity, wherein the LITT circumferential ablation probe is connected to a helium-neon laser with a laser wavelength of 632.8nm, and a slit diaphragm is provided between the laser measurement sensor and the LITT circumferential ablation probe, so The slit size of the slit diaphragm is 0.3mm; and the motion drive controller controls the motion driver to drive the diaphragm and the laser measurement sensor to perform circumferential and axial movements along the tapered surface of the LITT circumferential ablation probe. to obtain the spatial intensity distribution of the laser light emitted by the LITT circumferential ablation probe, wherein the aperture and the laser measurement sensor are fixedly connected to the motion driver.
本说明书另一个方面提供一种制备光纤布拉格光栅(FBG)传感器的方法，其特征在于，所述方法包括：将制备所述FBG传感器的原材料固定于固定器件，所述固定器件固定连接于运动驱动器；由激光器控制器控制激光器发射激光，所述激光依次经过光束校正装置，狭缝光阑，紫外镀膜透镜和相位掩膜后，在所述原材料表面产生条带状光斑；以及由运动驱动控制器控制运动驱动器，驱动所述原材料运动，在所述原材料运动过程中，通过所述激光照射所述原材料，从而形成所述FBG传感器。Another aspect of this specification provides a method for preparing a fiber Bragg grating (FBG) sensor, which is characterized in that the method includes: fixing the raw material for preparing the FBG sensor to a fixing device, and the fixing device is fixedly connected to a motion driver ; The laser controller controls the laser to emit laser, and the laser passes through the beam correction device, the slit diaphragm, the ultraviolet coating lens and the phase mask in sequence, and generates strip-shaped light spots on the surface of the raw material; and the motion drives the controller A motion driver is controlled to drive the raw material to move. During the movement of the raw material, the raw material is irradiated by the laser, thereby forming the FBG sensor.
在一些实施例中，所述激光器为248nm特征波长的准分子脉冲激光器，所述激光器产生的激光为248nm中央波长，脉冲持续时间15ns的矩形平顶光束。In some embodiments, the laser is an excimer pulse laser with a characteristic wavelength of 248 nm, and the laser generated by the laser is a rectangular flat-top beam with a central wavelength of 248 nm and a pulse duration of 15 ns.
在一些实施例中，所述光束校正装置包括两个248nm特征波长准分子激光45°线镜，所述狭缝光阑包括4.5mm宽度可调的机械狭缝装置，所述紫外镀膜透镜包括245-440nm特征波长紫外镀膜熔融石英平凸圆柱透镜，所述相位掩膜包括紫外辐照248nm特征波长1460-1600nm超带宽相位掩膜，所述条带状光斑的宽度为20mm，高度为32.4μm。In some embodiments, the beam correction device includes two 248nm characteristic wavelength excimer laser 45° line mirrors, the slit diaphragm includes a 4.5mm width adjustable mechanical slit device, and the UV-coated lens includes 245 -440nm characteristic wavelength UV-coated fused silica plano-convex cylindrical lens, the phase mask includes ultraviolet irradiation 248nm characteristic wavelength 1460-1600nm ultra-bandwidth phase mask, the strip-shaped light spot has a width of 20mm and a height of 32.4μm.
在一些实施例中，制备所述FBG传感器的原材料需满足：材料截止波长≤1280nm，1310nm时最大衰减标准取样≤0.35dB/km，1625nm时最大衰减标准取样≤0.23dB/km，1310nm时光纤模场直径(MFD)模式场外径＝9.2±0.4μm，1550nm时MFD模式场外径＝10.4±0.5μm，1550nm时色散≤18ps/(nm.km)，1625nm时色散≤22ps/(nm.km)，1310nm和1550nm时点不连续性≤0.05dB，1310nm时有效折射率群1.467，1550nm时有效折射率群1.4677，1310nm时瑞丽背向散射系数-77dB，以及1550nm时瑞丽背向散射系数-82dB。In some embodiments, the raw materials for preparing the FBG sensor need to meet the following requirements: material cut-off wavelength ≤ 1280nm, maximum attenuation standard sampling at 1310nm ≤ 0.35dB/km, maximum attenuation standard sampling at 1625nm ≤ 0.23dB/km, fiber mode at 1310nm Field diameter (MFD) mode field outer diameter=9.2±0.4μm, MFD mode field outer diameter=10.4±0.5μm at 1550nm, dispersion ≤18ps/(nm.km) at 1550nm, dispersion ≤22ps/(nm.km) at 1625nm ), point discontinuity at 1310nm and 1550nm ≤ 0.05dB, effective refractive index group at 1310nm 1.467, effective refractive index group at 1550nm 1.4677, Ruili backscattering coefficient at 1310nm -77dB, and Ruili backscattering coefficient at 1550nm -82dB .
[1]本说明书另一个方面提供一种医学治疗装置，包括：磁共振成像(MRI)设备，被配置为对包括目标对象的特定区域进行成像，生成磁共振图像；激光间质热疗(LITT)设备，包括LITT探针，基于所述磁共振图像，所述LITT探针靠近所述目标对象，并通过发射激光对所述目标对象进行治疗；和光纤布拉格光栅(FBG)传感器，被配置为获取所述目标对象的温度，其中，所述FBG传感器是根据上述制备FBG传感器的方法制备而成的。[1] Another aspect of this specification provides a medical treatment device, including: a magnetic resonance imaging (MRI) device configured to image a specific area including a target object to generate a magnetic resonance image; laser interstitial thermotherapy (LITT) ) device, including a LITT probe that is close to the target object and treats the target object by emitting laser light based on the magnetic resonance image; and a fiber Bragg grating (FBG) sensor configured to Obtain the temperature of the target object, wherein the FBG sensor is prepared according to the above method of preparing an FBG sensor.
在一些实施例中，所述FBG传感器靠近所述目标对象，确定所述目标对象的温度变化，其中，所述目标对象的温度变化是基于获取的FBG的热敏性S FSG，通过对布拉格波长漂移Δλ S与温度变化ΔT之间的关系进行校准而确定的。 In some embodiments, the FBG sensor is close to the target object and determines a temperature change of the target object, wherein the temperature change of the target object is based on the acquired thermal sensitivity S FSG of the FBG, by adjusting the Bragg wavelength drift Δλ The relationship between S and temperature change ΔT is determined by calibration.
在一些实施例中，对布拉格波长漂移Δλ S与温度变化ΔT之间的关系是通过将所述FBG传感器置于温度控制器内，所述温度控制器的温度间歇性变化，同时，由放大自发辐射(ASE)激光器通过环形器，到达所述FBG传感器，所述FBG传感器的反射信号通过所述环形器进入电信光谱分析仪，所述电信光谱分析仪监测所述FBG传感器的反射光谱从而确定的。 In some embodiments, the relationship between the Bragg wavelength shift Δλ S and the temperature change ΔT is obtained by placing the FBG sensor in a temperature controller, the temperature of the temperature controller changes intermittently, and at the same time, the amplified spontaneous The radiation (ASE) laser passes through the circulator and reaches the FBG sensor. The reflection signal of the FBG sensor enters the telecommunications spectrum analyzer through the circulator. The telecommunications spectrum analyzer monitors the reflection spectrum of the FBG sensor to determine .
本说明书又一个方面提供一种光学相干断层成像(OCT)探针，包括：输入端口，被配置为将光源发出的光束输入至所述OCT探针；第一透镜，被配置为对入射所述OCT探针的光束进行扩束；第二透镜，设置于所述第一透镜的后级，被配置为对出射所述第一透镜的光束进行消色差和聚焦；和光束偏转单元，设置于所述第二透镜的后级，被配置为对出射所述第二透镜的光束进行偏转出射，所述光束偏转单元包括针芯和位于针芯外周的硬质包层，所述光束偏转单元包括斜切端面，所述斜切端面涂覆有金属镀层。Another aspect of this specification provides an optical coherence tomography (OCT) probe, including: an input port configured to input a light beam emitted by a light source to the OCT probe; a first lens configured to incident the The beam of the OCT probe is beam expanded; a second lens is provided at the downstream stage of the first lens and is configured to achromatize and focus the light beam that exits the first lens; and a beam deflection unit is provided at the The rear stage of the second lens is configured to deflect the light beam exiting the second lens. The light beam deflection unit includes a needle core and a hard cladding located on the outer periphery of the needle core. The beam deflection unit includes an oblique The beveled end surface is coated with a metal plating layer.
在一些实施例中，所述第一透镜为无芯透镜，所述OCT探针的焦距及光斑大小与所述无芯透镜的长度与所述OCT探针的焦距及光斑大小相关。In some embodiments, the first lens is a coreless lens, and the focal length and spot size of the OCT probe are related to the length of the coreless lens and the focal length and spot size of the OCT probe.
在一些实施例中，所述第二透镜为微平凸球面柱透镜，所述微平凸球面柱透镜沿轴向的始端为平面，末端为球面，所述平面的角度为0°或8°，所述球面的曲率为-1.8mm，所述微平凸球面柱透镜的柱面直径为560μm。In some embodiments, the second lens is a slightly plano-convex spherical cylindrical lens, the starting end of the slightly plano-convex spherical cylindrical lens along the axial direction is a plane, the end is a sphere, the angle of the plane is 0° or 8°, the curvature of the sphere is -1.8 mm, and the cylindrical diameter of the slightly plano-convex spherical cylindrical lens is 560 μm.
在一些实施例中，所述光束偏转单元的截断轴向柱体长度为5μm。In some embodiments, the beam deflection unit has a truncated axial cylinder length of 5 μm.
在一些实施例中，所述OCT探针进一步包括弹簧扭力线圈，设置于所述OCT探针前端；光学套管，所述第一透镜、第二透镜、光束偏转单元及所述弹簧扭力线圈容纳于所述光学套管中；和填充体，填充于所述光学套管内部，使所述第一透镜、第二透镜、光束偏转单元相对于所述光学套管固定。In some embodiments, the OCT probe further includes a spring torsion coil disposed at the front end of the OCT probe; an optical sleeve housing the first lens, the second lens, the beam deflection unit and the spring torsion coil. in the optical sleeve; and a filling body filled inside the optical sleeve to fix the first lens, the second lens, and the beam deflection unit relative to the optical sleeve.
本说明书又一个方面提供一种医学治疗装置，包括：磁共振成像(MRI)设备，被配置为对包括目标对象的特定区域进行成像，生成磁共振图像；激光间质热疗(LITT)设备，包括LITT探针，基于所述磁共振图像，所述LITT探针靠近所述目标对象，并通过发射激光对所述目标对象进行治疗；和光学相干断层成像(OCT)设备，被配置为对所述目标对象进行成像，所述OCT设备包括上述的OCT探针。Yet another aspect of the present specification provides a medical treatment apparatus, comprising: a magnetic resonance imaging (MRI) device, configured to image a specific area including a target object and generate a magnetic resonance image; a laser interstitial thermal therapy (LITT) device, comprising a LITT probe, based on the magnetic resonance image, the LITT probe approaches the target object and treats the target object by emitting laser; and an optical coherence tomography (OCT) device, configured to image the target object, the OCT device comprising the above-mentioned OCT probe.
本说明书又一个方面提供一种医学治疗装置。所述医学治疗装置包括：磁共振成像(MRI)设备，被配置为对包括目标对象的特定区域进行成像，生成磁共振图像；激光间质热疗(LITT)设备，包括LITT探针，基于所述磁共振图像，所述LITT探针靠近所述目标对象，并通过发射激光对所述目标对象进行治疗；和测温元件，被配置为获取所述目标对象边缘上特定位置的温度，所述特定位置为所述目标对象边缘上距离所述LITT探针最远的位置。In yet another aspect, this specification provides a medical treatment device. The medical treatment device includes: a magnetic resonance imaging (MRI) device configured to image a specific area including a target object and generate a magnetic resonance image; a laser interstitial thermal therapy (LITT) device including a LITT probe based on the The magnetic resonance image, the LITT probe is close to the target object and treats the target object by emitting laser; and a temperature measurement element configured to obtain the temperature of a specific position on the edge of the target object, the The specific position is the farthest position from the LITT probe on the edge of the target object.
在一些实施例中，所述测温元件包括LITT光子测温探针。In some embodiments, the temperature measurement element includes a LITT photon temperature measurement probe.
在一些实施例中，所述医学治疗装置进一步包括处理模块，所述处理模块被配置为当所述测温元件测得的温度超出预设温度范围时，基于测得的温度与所述预设温度范围的差值，确定所述LITT设备的目标激光输出剂量值，使得所述测温元件测得的温度处于所述预设温度范围。In some embodiments, the medical treatment device further includes a processing module configured to, when the temperature measured by the temperature measuring element exceeds the preset temperature range, based on the measured temperature and the preset temperature range. The difference between the temperature ranges determines the target laser output dose value of the LITT device so that the temperature measured by the temperature measuring element is within the preset temperature range.
在一些实施例中，所述医学治疗装置进一步包括激光功率衰减器，被配置为将当前激光输出剂量值调整为所述目标激光输出剂量值。In some embodiments, the medical treatment device further includes a laser power attenuator configured to adjust the current laser output dose value to the target laser output dose value.
在一些实施例中，所述激光功率衰减器通过动态调整所述当前激光输出剂量值，使得测温元件测得的温度始终处于所述预设温度范围。In some embodiments, the laser power attenuator dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measuring element is always within the preset temperature range.
在一些实施例中，所述预设温度范围为46±1℃。In some embodiments, the preset temperature range is 46±1°C.
在一些实施例中，所述LITT探针为LITT侧向消融探针或LITT周向消融探针。In some embodiments, the LITT probe is a LITT lateral ablation probe or a LITT circumferential ablation probe.
在一些实施例中，所述LITT周向消融探针设置于所述目标对象的等效中心，所述测温元件设置于所述目标对象边缘上距离所述LITT周向消融探针最远处的位置，所述LITT周向消融探针与所述测温元件的距离等于或接近所述目标对象的等效半径。In some embodiments, the LITT circumferential ablation probe is disposed at the equivalent center of the target object, and the temperature measurement element is disposed on the edge of the target object farthest from the LITT circumferential ablation probe. The distance between the LITT circumferential ablation probe and the temperature measuring element is equal to or close to the equivalent radius of the target object.
在一些实施例中，所述LITT侧向消融探针设置于所述目标对象的一侧边缘，所述测温元件设置于所述目标对象的相对一侧的边缘上距离所述LITT侧向消融探针最远处的位置，所述LITT侧向消融探针与所述测温元件的距离等于或接近所述目标对象的等效直径。In some embodiments, the LITT lateral ablation probe is disposed on one edge of the target object, and the temperature measurement element is disposed on the edge of the opposite side of the target object at a distance from the LITT lateral ablation probe. At the farthest position of the probe, the distance between the LITT lateral ablation probe and the temperature measurement element is equal to or close to the equivalent diameter of the target object.
在一些实施例中，所述医学治疗装置进一步包括光学相干断层成像(OCT)设备，被配置为对所述目标对象进行成像，生成OCT图像。In some embodiments, the medical treatment apparatus further comprises an optical coherence tomography (OCT) device configured to image the target object and generate an OCT image.
在一些实施例中，所述OCT设备包括OCT探针，所述OCT探针向所述目标对象发射光信号，用以对治疗过程中的所述目标对象进行成像，所述OCT探针发射的光信号具有两种不同的中央波长。In some embodiments, the OCT device includes an OCT probe that emits a light signal to the target object to image the target object during treatment, and the OCT probe emits a light signal. The optical signal has two different central wavelengths.
在一些实施例中，所述医学治疗装置进一步包括第一驱动装置，耦合于所述LITT探针，并控制所述LITT探针的平移运动和旋转运动；和第二驱动装置，耦合于所述测温元件，并控制所述测温元件的平移运动。In some embodiments, the medical treatment device further includes a first driving device coupled to the LITT probe and controlling the translational movement and rotational movement of the LITT probe; and a second driving device coupled to the LITT probe. temperature measuring element, and control the translational movement of the temperature measuring element.
在一些实施例中，所述第一驱动装置包括第一平移线缆和第一旋转线缆，以及第一平移控制机构和第一旋转控制机构，其中，所述第一平移线缆和第一旋转线缆分别连接于所述第一平移控制机构和第一旋转控制机构，所 述第一平移控制机构和第一旋转控制机构连接于所述LITT探针，通过所述第一平移线缆和所述第一旋转线缆，分别控制所述LITT探针的平移运动和旋转运动。In some embodiments, the first driving device includes a first translation cable and a first rotation cable, and a first translation control mechanism and a first rotation control mechanism, wherein the first translation cable and the first rotation control mechanism The rotation cables are respectively connected to the first translation control mechanism and the first rotation control mechanism. The first translation control mechanism and the first rotation control mechanism are connected to the LITT probe. Through the first translation cable and The first rotation cable controls the translational movement and rotational movement of the LITT probe respectively.
在一些实施例中，所述第二驱动装置包括第二平移线缆；和第二平移控制机构，其中，所述第二平移线缆连接于所述第二平移控制机构，所述第二平移控制机构连接于所述测温元件，通过所述第二平移线缆控制所述测温元件的平移运动。In some embodiments, the second driving device includes a second translation cable; and a second translation control mechanism, wherein the second translation cable is connected to the second translation control mechanism, and the second translation A control mechanism is connected to the temperature measuring element and controls the translational movement of the temperature measuring element through the second translation cable.
附图说明BRIEF DESCRIPTION OF THE DRAWINGS
本说明书将以示例性实施例的方式进一步说明，这些示例性实施例将通过附图进行详细描述。这些实施例并非限制性的，在这些实施例中，相同的编号表示相同的结构，其中：This specification is further explained by way of example embodiments, which are described in detail by means of the accompanying drawings. These embodiments are not limiting. In these embodiments, the same numbers represent the same structures, where:
图1是根据本说明书一些实施例所示的医学治疗系统。Figure 1 is a medical treatment system according to some embodiments of the present specification.
图2A-2D是根据本说明书一些实施例所示的医学治疗装置的示例性结构图。2A-2D are exemplary structural diagrams of medical treatment devices according to some embodiments of the present specification.
图3A和3B是根据本说明书一些实施例的示例性驱动装置的结构示意图。3A and 3B are structural schematic diagrams of an exemplary driving device according to some embodiments of this specification.
图4A-4C是根据本说明书一些实施例的示例性平移控制机构和/或旋转控制机构的结构示意图。4A-4C are structural schematic diagrams of exemplary translation control mechanisms and/or rotation control mechanisms according to some embodiments of this specification.
图5是根据本说明书一些实施例所示的控制设备的示例性结构图Figure 5 is an exemplary structural diagram of a control device according to some embodiments of this specification.
图6是根据本说明书一些实施例的示例性两种不同类型的集成探针。Figure 6 is an illustration of two different types of integrated probes in accordance with some embodiments of the present specification.
图7所示为根据本说明书一些实施例的通过第一种工艺制备的示例性LITT侧向消融探针。Figure 7 shows an exemplary LITT lateral ablation probe prepared by the first process according to some embodiments of the present specification.
图8所示为根据本说明书一些实施例的通过第二种工艺制备的示例性LITT侧向消融针芯。Figure 8 shows an exemplary LITT lateral ablation core prepared by the second process according to some embodiments of the present specification.
图9所示为根据本说明书一些实施例的示例性LITT周向消融探针。Figure 9 illustrates an exemplary LITT circumferential ablation probe in accordance with some embodiments of the present specification.
图10是根据本说明书一些实施例所示的示例性锥形面加工示意图Figure 10 is a schematic diagram of an exemplary tapered surface processing according to some embodiments of the present specification.
图11是根据本说明书一些实施例所示的示例性交叉螺纹状分布的凹槽的加工示意图。11 is a schematic diagram of processing of exemplary cross-threaded grooves according to some embodiments of the present specification.
图12是根据本说明书一些实施例所示的测试LITT周向消融探针的矢量光能分布的示意图。Figure 12 is a schematic diagram of vector light energy distribution of a LITT circumferential ablation probe tested according to some embodiments of this specification.
图13是根据本说明书一些实施例所示的利用热电偶测温的示意图。Figure 13 is a schematic diagram of temperature measurement using a thermocouple according to some embodiments of this specification.
图14是根据本说明书一些实施例所示的利用FBG传感器测温的示意图。Figure 14 is a schematic diagram of temperature measurement using an FBG sensor according to some embodiments of this specification.
图15是根据本说明书一些实施例所示的示例性OCT探针。Figure 15 is an exemplary OCT probe according to some embodiments of the present specification.
图16是根据本说明书一些实施例所示的制备FBG传感器的示意图。Figure 16 is a schematic diagram of preparing an FBG sensor according to some embodiments of this specification.
图17是根据本说明书另一些实施例所示的医学治疗装置的示意图。Figure 17 is a schematic diagram of a medical treatment device according to other embodiments of this specification.
图18是根据本说明书一些实施例所示的LITT光子测温探针的示意图。Figure 18 is a schematic diagram of a LITT photon temperature measurement probe according to some embodiments of the present specification.
图19是根据本说明书一些实施例所示的LITT光子消融探针的示意图。Figure 19 is a schematic diagram of a LITT photon ablation probe according to some embodiments of the present specification.
图20是根据本说明书一些实施例所示的治疗时LITT光子消融探针及LITT光子测温探针的示意图。FIG. 20 is a schematic diagram of a LITT photon ablation probe and a LITT photon temperature measurement probe during treatment according to some embodiments of the present specification.
图中：In the picture:
100：医学治疗系统，110：MRI设备，120：LITT设备，130：测温元件，140：控制设备，150：终端，200：医学治疗装置，201：支撑固定平台，202：MRI设备，203：头部线圈，204：驱动装置，205：接口平台，206：控制中继平台，207：集成元件，208：控制设备，209：终端，210：LITT探针位移控制器，211：光路中继处理装置，212：光纤滑环装置，213：冷却控制元件，214：冷却通道，215：平移线缆，216：旋转线缆，217：平移控制机构，218：旋转控制机构，219：OCT探针通道，220：LITT探针通道，221：测温元件控制线缆通道，222：位移传感器线缆通道，223：集成管路，224：集成探针，301：动力输入端，302：线缆，303：线缆，304：动力输出端，305：驱动旋钮，306：驱动旋钮，307：锥齿轮，308：锥齿轮，401：蜗轮蜗杆组件，402：同步带传动组件，403：同步带传动组件，404：LITT探针通道，501：OCT成像控制模块，502：LITT治疗控制模块，503：测温元件温控模块，504：头部线圈成像配准模块，505：冷却系统控制模块，506：LITT探针位置传感控制模块，507：驱动控制模块，508：支撑固定平台控制模块，601：接口，610：LITT侧向消融集成探针，611：测温元件，612：CO 2送气管，613：LITT侧向消融探针，614：OCT探针，615：CO 2集气管，660：LITT周向消融集成探针，661：测温元件，662：CO 2送气管，663：LITT周向消融探针，664：OCT探针，665：CO 2集气管，700：LITT侧向 消融探针，710：探针主体，720：连接面，730：镀层，800：LITT侧向消融探针，810：探针主体，820：连接面，830：透镜，900：LITT周向消融探针，910：探针主体，920：锥形面，1000：雕锥设备，1001：终端，1002：激光器控制器，1003：激光器，1004-1：反射镜，1004-2：反射镜，1005：快门，1006：快门控制器，1007：激光功率衰减器，1008：衍射分束透镜单元，1009：聚焦透镜单元，1010：滑轨，1011：固定器件，1012：运动驱动器，1013：运动驱动控制器，1014-1：光斑，1014-2：光斑，1015：将待雕锥工件，1100：雕花设备，1101：终端，1102：激光器控制器，1103：激光器，1104：反射镜，1105：透镜组，1106：滑轨，1107：固定器件，1108：运动驱动器，1109：运动驱动控制器，1110：待雕花工件，1200：LITT探针极性测试设备，1201：激光器，1202：光纤耦合器，1203：LITT周向消融集成探针，1204：光阑，1205：激光测量传感器，1206：终端，1207：运动驱动器，1208：运动驱动控制器，1301：终端，1302：供电采集模块，1303：热电偶，1401：终端，1402：ASE激光器，1403：环形器，1404-1：FBG传感器，1404-2：FBG传感器，1405：电信光谱分析仪，1406：温度控制器，1500：OCT探针，1501：输入端口，1502：第一透镜，1504：第二透镜，1506：光束偏转单元，1508：弹簧扭力线圈，1510：光学套管，1512：填充体，1600：FBG辐照设备，1601：终端，1602：激光器控制器，1603：激光器，1604-1：光束校正装置，1604-2：光束校正装置，1605：狭缝光阑，1606：紫外镀膜透镜，1607：相位掩膜，1608：滑轨，1609：滑轨，1610：固定器件，1611：运动驱动器，1612：运动驱动控制器，1700：医学治疗装置，1710：控制设备，1711：OCT控制模块，1713：LITT控制模块，1715：FBG控制模块，1717：探针传感模块，1719：驱动控制模块，1720：接口平台集线控制模组，1722：光纤滑环装置，1724：光路中继处理装置，1726：位移控制器，1730：驱动组件，1732：第一驱动装置，1734：第二驱动装置，1736：双轴立体框架，1738：单轴立体框架，1740：探针组，1742：LITT光子消融探针，1744：LITT光子测温探针，1750：温度反馈控制单元，1760：激光剂量控制单元，1770：衰减器调节控制单元，1780：衰减器调节单元，1790：激光功率衰减器，1805：LITT光子测温探针，1810：驱动马达，1815：驱动线缆，1820：单轴立体框架，1825：位移传感器线缆通道，1830：LITT测温探针通道，1835：集成元件，1910：LITT光子侧向消融探针，1912：OCT探针，1914：LITT侧向消融探针，1920：LITT光子周向消融探针，1922：OCT探针，1924：LITT周向消融探针，1930：驱动马达，1935：驱动线缆，1940：驱动线缆，1945：双轴立体框架，1950：位移传感器线缆通道，1955：LITT消融探针通道，1960：OCT探针通道，2010：LITT光子测温探针，2020：LITT光子周向消融探针，2030：LITT光子侧向消融探针。 100: Medical treatment system, 110: MRI equipment, 120: LITT equipment, 130: Temperature measurement element, 140: Control equipment, 150: Terminal, 200: Medical treatment device, 201: Support fixed platform, 202: MRI equipment, 203: Head coil, 204: driving device, 205: interface platform, 206: control relay platform, 207: integrated components, 208: control equipment, 209: terminal, 210: LITT probe displacement controller, 211: optical path relay processing Device, 212: Optical fiber slip ring device, 213: Cooling control element, 214: Cooling channel, 215: Translation cable, 216: Rotation cable, 217: Translation control mechanism, 218: Rotation control mechanism, 219: OCT probe channel , 220: LITT probe channel, 221: Temperature measuring element control cable channel, 222: Displacement sensor cable channel, 223: Integrated pipeline, 224: Integrated probe, 301: Power input terminal, 302: Cable, 303 : Cable, 304: Power output end, 305: Drive knob, 306: Drive knob, 307: Bevel gear, 308: Bevel gear, 401: Worm gear assembly, 402: Timing belt transmission assembly, 403: Timing belt transmission assembly, 404: LITT probe channel, 501: OCT imaging control module, 502: LITT treatment control module, 503: Temperature measurement element temperature control module, 504: Head coil imaging registration module, 505: Cooling system control module, 506: LITT Probe position sensing control module, 507: drive control module, 508: support fixed platform control module, 601: interface, 610: LITT lateral ablation integrated probe, 611: temperature measurement element, 612: CO2 air supply tube, 613 : LITT lateral ablation probe, 614: OCT probe, 615: CO 2 air collecting tube, 660: LITT circumferential ablation integrated probe, 661: temperature measurement element, 662: CO 2 air supply tube, 663: LITT circumferential ablation Probe, 664: OCT probe, 665: CO 2 trachea collection tube, 700: LITT lateral ablation probe, 710: Probe body, 720: Connection surface, 730: Coating, 800: LITT lateral ablation probe, 810 : Probe body, 820: Connection surface, 830: Lens, 900: LITT circumferential ablation probe, 910: Probe body, 920: Taper surface, 1000: Cone engraving equipment, 1001: Terminal, 1002: Laser controller , 1003: Laser, 1004-1: Reflector, 1004-2: Reflector, 1005: Shutter, 1006: Shutter controller, 1007: Laser power attenuator, 1008: Diffraction beam splitting lens unit, 1009: Focusing lens unit, 1010: Slide rail, 1011: Fixed device, 1012: Motion driver, 1013: Motion drive controller, 1014-1: Light spot, 1014-2: Light spot, 1015: Cone workpiece to be carved, 1100: Engraving equipment, 1101: Terminal , 1102: Laser controller, 1103: Laser, 1104: Reflector, 1105: Lens group, 1106: Slide rail, 1107: Fixed device, 1108: Motion driver, 1109: Motion drive controller, 1110: Workpiece to be carved, 1200 : LITT probe polarity testing equipment, 1201: laser, 1202: fiber coupler, 1203: LITT circumferential ablation integrated probe, 1204: aperture, 1205: laser measurement sensor, 1206: terminal, 1207: motion driver, 1208 : Motion drive controller, 1301: Terminal, 1302: Power supply acquisition module, 1303: Thermocouple, 1401: Terminal, 1402: ASE laser, 1403: Circulator, 1404-1: FBG sensor, 1404-2: FBG sensor, 1405 : Telecommunications spectrum analyzer, 1406: Temperature controller, 1500: OCT probe, 1501: Input port, 1502: First lens, 1504: Second lens, 1506: Beam deflection unit, 1508: Spring torsion coil, 1510: Optics Casing, 1512: filling body, 1600: FBG irradiation equipment, 1601: terminal, 1602: laser controller, 1603: laser, 1604-1: beam correction device, 1604-2: beam correction device, 1605: slit light Lan, 1606: UV coated lens, 1607: Phase mask, 1608: Slide rail, 1609: Slide rail, 1610: Fixed device, 1611: Motion driver, 1612: Motion drive controller, 1700: Medical treatment device, 1710: Control Equipment, 1711: OCT control module, 1713: LITT control module, 1715: FBG control module, 1717: Probe sensing module, 1719: Drive control module, 1720: Interface platform centralized control module, 1722: Optical fiber slip ring device , 1724: Optical path relay processing device, 1726: Displacement controller, 1730: Driving assembly, 1732: First driving device, 1734: Second driving device, 1736: Biaxial three-dimensional frame, 1738: Single-axis three-dimensional frame, 1740: Probe set, 1742: LITT photon ablation probe, 1744: LITT photon temperature measurement probe, 1750: temperature feedback control unit, 1760: laser dose control unit, 1770: attenuator adjustment control unit, 1780: attenuator adjustment unit, 1790: Laser power attenuator, 1805: LITT photon temperature measurement probe, 1810: Drive motor, 1815: Drive cable, 1820: Single-axis three-dimensional frame, 1825: Displacement sensor cable channel, 1830: LITT temperature measurement probe channel , 1835: integrated components, 1910: LITT photon lateral ablation probe, 1912: OCT probe, 1914: LITT lateral ablation probe, 1920: LITT photon circumferential ablation probe, 1922: OCT probe, 1924: LITT Circumferential ablation probe, 1930: drive motor, 1935: drive cable, 1940: drive cable, 1945: biaxial three-dimensional frame, 1950: displacement sensor cable channel, 1955: LITT ablation probe channel, 1960: OCT detector Needle channel, 2010: LITT photon thermometry probe, 2020: LITT photon circumferential ablation probe, 2030: LITT photon lateral ablation probe.
具体实施方式Detailed ways
为了更清楚地说明本说明书实施例的技术方案，下面将对实施例描述中所需要使用的附图作简单的介绍。显而易见地，下面描述中的附图仅仅是本说明书的一些示例或实施例，对于本领域的普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图将本说明书应用于其它类似情景。除非从语言环境中显而易见或另做说明，图中相同标号代表相同结构或操作。应当理解，本文使用的“系统”、“装置”、“单元”和/或“模块”是用于区分不同级别的不同组件、元件、部件、部分或装配的一种方法。然而，如果其他词语可实现相同的目的，则可通过其他表达来替换所述词语。In order to explain the technical solutions of the embodiments of this specification more clearly, the accompanying drawings needed to be used in the description of the embodiments will be briefly introduced below. Obviously, the drawings in the following description are only some examples or embodiments of this specification. For those of ordinary skill in the art, without exerting any creative efforts, this specification can also be applied to other applications based on these drawings. Other similar scenarios. Unless obvious from the locale or otherwise stated, the same reference numbers in the figures represent the same structure or operation. It will be understood that the terms "system", "apparatus", "unit" and/or "module" as used herein are a means of distinguishing between different components, elements, parts, portions or assemblies at different levels. However, said words may be replaced by other expressions if they serve the same purpose.
如本说明书和权利要求书中所示，除非上下文明确提示例外情形，“一”、“一个”、“一种”和/或“该”等词并非特指单数，也可包括复数。一般说来，术语“包括”与“包含”仅提示包括已明确标识的步骤和元素，而这些步骤和元素不构成一个排它性的罗列，方法或者设备也可能包含其它的步骤或元素。As shown in this specification and claims, words such as "a", "an", "an" and/or "the" do not specifically refer to the singular and may include the plural unless the context clearly indicates an exception. Generally speaking, the terms "comprising" and "comprising" only imply the inclusion of clearly identified steps and elements, and these steps and elements do not constitute an exclusive list. The method or apparatus may also include other steps or elements.
图1是根据本说明书一些实施例所示的医学治疗系统。FIG. 1 is a diagram showing a medical treatment system according to some embodiments of the present specification.
医学治疗系统100用于对目标对象进行医学诊断和/或治疗。所述目标对象可以包括生物对象(如人体、动物等)。例如，目标对象可以包括人体或其特定部分，如头部，和/或待治疗的组织、病灶(如脑肿瘤和癫痫病灶)等，或其组合。为了便于理解医学治疗系统100的具体结构，下文以磁共振引导(MRg)激光间质热疗(LITT)为例，对医学治疗系统100进行阐述。MRg-LITT可以通过磁共振成像(MRI)，确定目标对象(例如，肿瘤)的位置和大小，以此有效且可控地引导激光放射，对所述目标对象进行热疗。然而，医学治疗系统100并不限于 MRg-LITT，也可以是其他类型的治疗系统，例如，MRg微波治疗等。The medical treatment system 100 is used for medical diagnosis and/or treatment of target objects. The target object may include biological objects (such as human body, animals, etc.). For example, the target object may include the human body or specific parts thereof, such as the head, and/or tissues to be treated, lesions (such as brain tumors and epileptic lesions), etc., or combinations thereof. In order to facilitate understanding of the specific structure of the medical treatment system 100 , the medical treatment system 100 will be described below using magnetic resonance guided (MRg) laser interstitial thermal therapy (LITT) as an example. MRg-LITT can determine the location and size of a target object (eg, a tumor) through magnetic resonance imaging (MRI), thereby effectively and controllably guiding laser radiation to perform thermal therapy on the target object. However, the medical treatment system 100 is not limited to MRg-LITT, and may also be other types of treatment systems, such as MRg microwave treatment, etc.
示例性地，如图1所示，医学治疗系统100包括MRI设备110，LITT设备120，测温元件130，控制设备140，、终端150以及光学相干断层成像(OCT)设备(图中未示出)。Exemplarily, as shown in Figure 1, the medical treatment system 100 includes an MRI device 110, a LITT device 120, a temperature measurement element 130, a control device 140, a terminal 150, and an optical coherence tomography (OCT) device (not shown in the figure). ).
MRI设备110被配置为对包含目标对象的特定区域进行扫描并生成MRI图像。MRI设备110可以MRI扫描仪。MRI扫描仪包括磁体模块和射频(RF)模块。磁体模块可以包括一个主磁场发生器和/或一个梯度磁场发生器。所述主磁场发生器可以包括在MRI扫描过程中产生静磁场B0的主磁体。所述主磁体可以采用永磁体、超导电磁体、电阻电磁体等。所述梯度磁场发生器可以在X、Y和/或Z方向上产生磁场梯度。此处所述X方向也可以被称为读出(RO)方向，所述Y方向也可以被称为相位编码(PE)方向，所述Z方向也可以被称为层面选择(SS)方向。所述梯度磁场可以编码所述目标对象的空间信息。RF模块可以包括RF发射线圈和/或接收线圈。所述RF发射线圈可以发射RF信号(或称为射频脉冲)，以激发感兴趣区域，产生MRI信号。所述RF接收线圈可以接收感兴趣区域发射的回波信号。在一些实施例中，所述RF信号可以是30°脉冲信号、40°脉冲信号、60°脉冲信号等。MRI设备110可以处理所述MRI信号，生成MRI图像。所述MRI图像可以表示包含所述目标对象的特定区域的解剖结构信息。The MRI device 110 is configured to scan a specific area containing a target object and generate an MRI image. The MRI device 110 may be an MRI scanner. The MRI scanner includes a magnet module and a radio frequency (RF) module. The magnet module may include a main magnetic field generator and/or a gradient magnetic field generator. The main magnetic field generator may include a main magnet that generates a static magnetic field B0 during an MRI scan. The main magnet may be a permanent magnet, a superconducting electromagnet, a resistive electromagnet, etc. The gradient magnetic field generator may generate a magnetic field gradient in the X, Y and/or Z directions. Here, the X direction may also be referred to as a readout (RO) direction, the Y direction may also be referred to as a phase encoding (PE) direction, and the Z direction may also be referred to as a slice selection (SS) direction. The gradient magnetic field may encode spatial information of the target object. The RF module may include an RF transmitting coil and/or a receiving coil. The RF transmitting coil may transmit an RF signal (or radio frequency pulse) to excite a region of interest and generate an MRI signal. The RF receiving coil may receive an echo signal emitted by the region of interest. In some embodiments, the RF signal may be a 30° pulse signal, a 40° pulse signal, a 60° pulse signal, etc. The MRI device 110 may process the MRI signals to generate an MRI image, which may represent anatomical structure information of a specific region of the target object.
在一些实施例中，磁体模块和/或RF模块的功能、尺寸、类型、几何形状、位置、数量可以根据一个或多个特定条件来确定或改变。例如，根据功能和尺寸的差异，RF线圈可以分为体线圈和局部线圈。所述体线圈可以设置为鸟笼线圈、横向电磁线圈、鞍形线圈等。所述局部线圈可以包括相控阵列线圈、环状线圈等。在一些实施例中，所述局部线圈可以包括霍姆赫兹头部线圈。霍姆赫兹头部线圈可以在患者头部区域制造小范围的均匀磁场，并发送RF信号及接收相应的头部MRI信号。所述头部MRI信号可以用于对患者头部进行成像，生成头部MRI图像。[2]在一些实施例中，MRI设备110还可以从所述MRI扫描仪获取热图像数据，用于磁共振热成像(MRTI)。基于所述热图像数据，重建热图像。所述热图像可以表示包含所述目标对象的特定区域的温度变化。在一些实施例中，所述热图像中每个像素/体素可以度量所述特定区域内对应位置的温度变化。In some embodiments, the functionality, size, type, geometry, location, and number of magnet modules and/or RF modules may be determined or changed based on one or more specific conditions. For example, RF coils can be divided into body coils and local coils based on differences in function and size. The body coil may be configured as a birdcage coil, a transverse electromagnetic coil, a saddle coil, or the like. The local coils may include phased array coils, loop coils, etc. In some embodiments, the local coils may include Holmhertz head coils. The Holmhertz head coil can create a small-scale uniform magnetic field in the patient's head area, send RF signals and receive corresponding head MRI signals. The head MRI signal can be used to image the patient's head to generate a head MRI image. [2] In some embodiments, the MRI device 110 can also acquire thermal image data from the MRI scanner for magnetic resonance thermography (MRTI). Based on the thermal image data, a thermal image is reconstructed. The thermal image may represent temperature changes in a specific area containing the target object. In some embodiments, each pixel/voxel in the thermal image can measure the temperature change at the corresponding location within the specific area.
LITT设备120被配置为产生激光，并利用激光的热效应，对目标对象进行治疗，例如消融目标对象。基于上述MRI图像和/或热图像，可以确定目标对象(例如，肿瘤)的位置和大小，从而有效且可控地引导LITT设备120放射激光，对所述目标对象进行热疗。The LITT device 120 is configured to generate laser light and utilize the thermal effect of the laser light to treat, eg, ablate, the target object. Based on the above-mentioned MRI images and/or thermal images, the location and size of the target object (eg, tumor) can be determined, thereby effectively and controllably guiding the LITT device 120 to emit laser light to perform thermal therapy on the target object.
LITT设备120包括激光器，LITT探针，以及连接所述激光器与所述LITT探针的通道(如光纤)及接口。所述激光器可以用于发射激光。所述激光器可以为固体激光器、气体激光器、液体激光器、半导体激光器、自由电子激光器等。在一些实施例中，所述激光器产生的激光的波长在一定范围内，例如，近红外区(0.75-2.5微米(μm))。所述激光器发射的激光通过所述光纤及接口，传输至所述LITT探针。The LITT device 120 includes a laser, a LITT probe, and a channel (such as an optical fiber) and an interface connecting the laser and the LITT probe. The laser can be used to emit laser light. The laser can be a solid laser, a gas laser, a liquid laser, a semiconductor laser, a free electron laser, etc. In some embodiments, the wavelength of the laser generated by the laser is within a certain range, for example, the near-infrared region (0.75-2.5 microns (μm)). The laser emitted by the laser is transmitted to the LITT probe through the optical fiber and the interface.
LITT探针，也称为LITT探头或LITT扩散施源器，作为治疗探针，用于将所述激光器产生的激光递送至所述目标对象，实现病灶的消融治疗。LITT探针包括探针主体。所述探针主体可以设置为不同结构。在不同结构下，激光出射的位置不同。具体地，根据所述出射位置的不同，LITT探针可以分为LITT侧向消融探针和LITT周向消融探针。LITT侧向消融探针是指激光出射位置位于探针端部(远端)的LITT探针。此时，激光出射的方向与LITT探针的轴向相同或呈一定角度。LITT周向消融探针是指激光出射位置均匀分布于探针周向的LITT探针。此时，激光出射的方向为LITT探针的径向，并围绕LITT探针周向均匀弥散。关于LITT探针的类型、具体结构及工艺，可以参照本申请中其他附图(例如，图6-11)及其描述，此处不再赘述。LITT probe, also called LITT probe or LITT diffusion applicator, is used as a treatment probe to deliver the laser light generated by the laser to the target object to achieve ablation treatment of lesions. The LITT probe includes the probe body. The probe body can be configured in different structures. Under different structures, the position of laser emission is different. Specifically, according to the difference in the exit position, the LITT probe can be divided into a LITT lateral ablation probe and a LITT circumferential ablation probe. A LITT lateral ablation probe refers to a LITT probe in which the laser emission position is located at the end (distal end) of the probe. At this time, the laser emission direction is the same as or at a certain angle with the axial direction of the LITT probe. LITT circumferential ablation probe refers to a LITT probe in which the laser emission position is evenly distributed in the circumference of the probe. At this time, the laser emission direction is the radial direction of the LITT probe, and is evenly dispersed around the circumference of the LITT probe. Regarding the type, specific structure and process of the LITT probe, reference can be made to other drawings (for example, Figures 6-11) and their descriptions in this application, which will not be described again here.
测温元件130用于对所述目标对象或其周边组织和/或LITT探针进行测温。例如，测温元件130可以接近所述目标对象，并获取所述目标对象及其周边组织的温度。基于所述目标对象及其周边组织的温度，LITT设备120可以以受控方式将热量通过LITT探针传递到所述目标对象，对目标对象进行治疗，保护所述目标对象周边的健康组织。The temperature measurement element 130 is used to measure the temperature of the target object or its surrounding tissue and/or the LITT probe. For example, the temperature measuring element 130 can be close to the target object and obtain the temperature of the target object and its surrounding tissues. Based on the temperature of the target object and its surrounding tissue, the LITT device 120 can transfer heat to the target object through the LITT probe in a controlled manner to treat the target object and protect the healthy tissue surrounding the target object.
测温元件130可以包括热电偶、光纤布拉格光栅(FBG)传感器等。热电偶可以直接测量温度，并将温度信号转换成成热电动势信号。所述热电动势信号可以进一步被转换成被测物体的温度。热电偶可以包括K型热电偶， T型热电偶，E型热电偶，S型热电偶，B型热电偶等。在一些实施例中，热电偶为K型热电偶。The temperature measurement element 130 may include a thermocouple, a fiber Bragg grating (FBG) sensor, or the like. Thermocouples can directly measure temperature and convert the temperature signal into a thermoelectromotive force signal. The thermoelectromotive force signal can be further converted into the temperature of the object being measured. Thermocouples can include K-type thermocouples, T-type thermocouples, E-type thermocouples, S-type thermocouples, B-type thermocouples, etc. In some embodiments, the thermocouple is a K-type thermocouple.
FBG传感器是将光纤特定位置制成折射率周期分布的光栅，以此光栅区作为传感区的传感器。特定波长的光波(布拉格反射光)在此光栅区内被反射。反射的中心波长信号与光栅周期和纤芯的有效折射率有关。当被测物体的温度发生变化时，光栅的周期和纤芯模的有效折射率发生变化，从而改变布拉格中心波长，通过光谱分析或其他波长解调技术对反射光的布拉格波长检测，即可获得温度发生的数值。The FBG sensor is a sensor in which a specific position of the optical fiber is made into a grating with a periodic distribution of refractive index, and the grating area is used as the sensing area. Light waves of specific wavelengths (Bragg reflected light) are reflected in this grating area. The reflected center wavelength signal is related to the grating period and the effective refractive index of the fiber core. When the temperature of the measured object changes, the period of the grating and the effective refractive index of the core mode change, thereby changing the Bragg center wavelength. By detecting the Bragg wavelength of the reflected light through spectral analysis or other wavelength demodulation techniques, it can be obtained The numerical value of the temperature occurrence.
控制设备140用于对医学治疗系统100的一个或多个部件进行控制，执行相应的操作。控制设备140可以基于控制的部件及需要执行的操作，生成相应的指令。所述指令以电信号的形式，传达至所控制的部件，使该部件执行相应的操作。示例性地，控制设备140可以接收通过终端150输入的请求或命令信息，以及MRI设备110和/或测温元件130生成信息(例如，图像、温度数据等)。基于上述信息，控制设备140可以生成控制指令。所述控制指令可以被发送至成LITT设备120，用于对目标对象进行治疗。The control device 140 is used to control one or more components of the medical treatment system 100 and perform corresponding operations. The control device 140 can generate corresponding instructions based on the components being controlled and the operations that need to be performed. The instructions are conveyed to the controlled component in the form of electrical signals, causing the component to perform corresponding operations. For example, the control device 140 may receive request or command information input through the terminal 150, and the MRI device 110 and/or the temperature measurement element 130 may generate information (eg, images, temperature data, etc.). Based on the above information, the control device 140 may generate control instructions. The control instructions may be sent to the LITT device 120 for treating the target subject.
在一些实施例中，控制设备140可以是微控制器(MCU)、中央处理器(CPU)、可编程逻辑器件(PLD)、专用集成电路(ASIC)、单片微型计算机(SCM)、系统芯片(SoC)等。In some embodiments, the control device 140 may be a microcontroller unit (MCU), a central processing unit (CPU), a programmable logic device (PLD), an application specific integrated circuit (ASIC), a single chip microcomputer (SCM), a system on chip (SoC), etc.
终端150可以用于信息(例如，图像、数据等)的输入/输出。终端150可以包括计算机、可移动设备(例如，手机、平板电脑、笔记本电脑)等，或其任意组合。在一些实施例中，终端150可以包括可穿戴设备、虚拟现实设备、增强现实设备等，或其任意组合。可穿戴设备包括手环、眼镜、头盔、手表等，或其任意组合。虚拟现实设备和/或增强现实设备包括虚拟现实头盔、虚拟现实眼镜、虚拟现实眼罩、增强现实头盔、增强现实眼镜、增强现实眼罩等，或其任意组合。例如，虚拟现实设备和/或增强现实设备可以包括Google Glass TM、Oculus Rift TM、Hololens TM、Gear VR TM等。在一些实施例中，终端150可以是控制设备140的一部分。 The terminal 150 may be used for input/output of information (eg, images, data, etc.). The terminal 150 may include a computer, a mobile device (eg, a mobile phone, a tablet, a laptop), etc., or any combination thereof. In some embodiments, the terminal 150 may include a wearable device, a virtual reality device, an augmented reality device, etc., or any combination thereof. Wearable devices include bracelets, glasses, helmets, watches, etc., or any combination thereof. Virtual reality devices and/or augmented reality devices include virtual reality helmets, virtual reality glasses, virtual reality goggles, augmented reality helmets, augmented reality glasses, augmented reality goggles, etc., or any combination thereof. For example, virtual reality devices and/or augmented reality devices may include Google Glass ™ , Oculus Rift ™ , Hololens ™ , Gear VR ™ , etc. In some embodiments, terminal 150 may be part of control device 140.
所述OCT设备利用宽带光源的低相干干涉，对所述目标对象进行成像，生成高分辨率(例如，微米级)和/或超深度的OCT图像。OCT设备包括时域光学相干层析成像(TDOCT)设备、谱域光学相干层析成像(SDOCT)设备和/或扫频光学相干层析成像(SSOCT)设备。The OCT device uses low-coherence interference of a broadband light source to image the target object and generate high-resolution (e.g., micrometer-level) and/or ultra-depth OCT images. The OCT device includes a time-domain optical coherence tomography (TDOCT) device, a spectral domain optical coherence tomography (SDOCT) device, and/or a swept-frequency optical coherence tomography (SSOCT) device.
在一些实施例中，所述OCT设备包括光源、OCT探针、干涉部件以及连接各部件的光纤及接口。所述光源采用低相干光源，以提高成像的纵向分辨率。所述OCT探针用于向目标对象发射所述光源射出的光线，并接收其反射的光线。光源发出的低相干光可以分为参考光与样品光(由OCT探针发出)，各自分别在经过参考镜反射与目标对象的组织反射(或后向反射)后，经由干涉部件发生干涉。基于干涉形成的干涉光谱，OCT设备(例如，其中的光电系统)可以获得所述目标对象的结构的深度信息。基于所述深度信息，可生成所述目标对象的OCT图像。所述OCT图像为二维或三维图像。所述OCT设备可以提供病理成像，结合LITT设备，可以实时探测消融病灶的癌化病理残余，并对消融灶切缘残留的癌化病理成像，进行快速的补充消融，使得癌化残余和复发的可能性降到最低。In some embodiments, the OCT device includes a light source, an OCT probe, an interference component, and optical fibers and interfaces connecting each component. The light source uses a low-coherence light source to improve the longitudinal resolution of imaging. The OCT probe is used to emit light emitted by the light source to a target object and receive light reflected by the light source. The low-coherence light emitted by the light source can be divided into reference light and sample light (emitted by the OCT probe). Each interferes through the interference component after being reflected by the reference mirror and reflected (or retroreflected) by the tissue of the target object. Based on the interference spectrum formed by the interference, the OCT device (for example, the optoelectronic system therein) can obtain depth information of the structure of the target object. Based on the depth information, an OCT image of the target object can be generated. The OCT image is a two-dimensional or three-dimensional image. The OCT device can provide pathological imaging. Combined with the LITT device, it can detect the cancerous pathological residue of the ablation lesion in real time, and perform rapid supplementary ablation on the remaining cancerous pathological imaging of the ablation lesion margin, so that the canceration residue and recurrence can be eliminated. The possibility is reduced to a minimum.
[3]医学治疗系统100的各设备或部件可以是本地的设备或部件，也可以是远程的设备或部件。各设备或部件以一种或多种各种方式连接。仅作为示例，控制设备140可以是远程设备，LITT设备110和MRI设备120可以通过网络连接到控制设备140。又例如，控制设备140可以是本地设备，LITT设备110和MRI设备120可以直接连接到控制设备140。作为进一步的示例，终端150可以直接或通过网络连接到控制设备140。所述网络可以包括促进医学治疗系统100的信息和/或数据交换的任何合适的网络。在一些实施例中，所述网络可以是和/或包括公共网络(例如互联网)、私有网络(例如局部区域网络(LAN)、广域网(WAN))、有线网络(例如以太网络)、无线网络(例如802.11网络、Wi-Fi网络)、蜂窝网络(例如、长期演进(LTE)网络)、帧中继网络、虚拟专用网(“VPN”)、卫星网络、电话网络、路由器、集线器、交换机、服务器计算机和/或其任何组合。仅作为示例，所述网络可以包括电缆网络、有线网络、光纤网络、电信网络、内联网、无线局部区域网络(WLAN)、城域网(MAN)、公共交换电话网(PSTN)、蓝牙TM网络、紫蜂TM网络、近场通信(NFC)网络等，或其任意组合。[3] Each device or component of the medical treatment system 100 may be a local device or component or a remote device or component. Each device or component is connected in one or more various ways. For example only, the control device 140 may be a remote device, and the LITT device 110 and the MRI device 120 may be connected to the control device 140 through a network. As another example, the control device 140 may be a local device, and the LITT device 110 and the MRI device 120 may be directly connected to the control device 140 . As a further example, terminal 150 may be connected to control device 140 directly or through a network. The network may include any suitable network that facilitates the exchange of information and/or data with the medical treatment system 100 . In some embodiments, the network may be and/or include a public network (eg, the Internet), a private network (eg, a local area network (LAN), a wide area network (WAN)), a wired network (eg, an Ethernet network), a wireless network (eg, an Ethernet network) (e.g., 802.11 networks, Wi-Fi networks), cellular networks (e.g., Long Term Evolution (LTE) networks), Frame Relay networks, virtual private networks (“VPNs”), satellite networks, telephone networks, routers, hubs, switches, servers Computer and/or any combination thereof. By way of example only, the network may include a cable network, a wired network, a fiber optic network, a telecommunications network, an intranet, a wireless local area network (WLAN), a metropolitan area network (MAN), a public switched telephone network (PSTN), a Bluetooth™ network , ZifengTM network, near field communication (NFC) network, etc., or any combination thereof.
应当注意的是，以上对于医学治疗系统100及其各部件/模块的描述，仅为描述方便，并不能把本申请限制在所举实施例范围之内。可以理解，对于本领域的技术人员来说，在了解该系统的原理后，可能在不背离这一原 理的情况下，可以对医学治疗系统100进行各种修正和改变，例如，对各个模块进行任意组合，或者构成子系统与其他模块连接。然而，这些修正和改变仍在本说明书的范围之内。It should be noted that the above description of the medical treatment system 100 and its components/modules is only for convenience of description and does not limit the present application to the scope of the embodiments. It can be understood that for those skilled in the art, after understanding the principle of the system, various modifications and changes may be made to the medical treatment system 100 without departing from this principle, for example, various modifications may be made to each module. Any combination, or form a subsystem to connect with other modules. However, such modifications and changes remain within the scope of this specification.
图2A-2D是根据本说明书一些实施例所示的医学治疗装置的示例性结构图。2A-2D are exemplary structural diagrams of medical treatment devices according to some embodiments of the present specification.
在一些实施例中，医学治疗装置200可以是将医学治疗系统100中(本地或远程的)各设备及部件进行集成的装置。如图所示，医学治疗装置200可以包括支撑固定平台201，MRI设备202，头部线圈203，LITT设备(图中未示出)，OCT设备(图中未示出)，测温元件(图中未示出)，冷却设备(图中未示出)，驱动装置204，接口平台205，控制中继平台206，集成元件207，控制设备208，和终端209。In some embodiments, the medical treatment device 200 may be a device that integrates various devices and components in the medical treatment system 100 (local or remote). As shown in the figure, the medical treatment device 200 may include a support fixed platform 201, an MRI device 202, a head coil 203, a LITT device (not shown in the figure), an OCT device (not shown in the figure), and a temperature measurement element (Fig. (not shown in the figure), cooling equipment (not shown in the figure), driving device 204, interface platform 205, control relay platform 206, integrated component 207, control device 208, and terminal 209.
支撑固定平台201，也称为治疗床，用于对患者进行支撑和/或固定，防止治疗过程中患者或其特定部位发生位移。在一些实施例中，支撑固定平台201可以在医学诊断和/或治疗过程中，基于控制设备208的发出的控制指令，进行运动(例如，平移、倾斜、旋转等)，以调整患者体位布局。例如，支撑固定平台201可以在MRI扫描成像过程中，基于控制设备208的发出的控制指令，进行平移或倾斜，为MRI提供更好的扫描位置基准。The support and fixation platform 201, also called a treatment bed, is used to support and/or fix the patient to prevent displacement of the patient or its specific parts during treatment. In some embodiments, the support and fixed platform 201 can move (eg, translate, tilt, rotate, etc.) based on control instructions issued by the control device 208 to adjust the patient's posture layout during medical diagnosis and/or treatment. For example, the support fixed platform 201 can translate or tilt based on the control instructions issued by the control device 208 during the MRI scanning and imaging process to provide a better scanning position reference for the MRI.
MRI设备202用于对包括目标对象(例如，患者脑部的肿瘤)的特定区域进行成像，生成MRI图像。所述MRI图像可以是实时MRI图像，也可以是非实时MRI图像。所述MRI图像可以包括三维图像或多个二维图像(例如，横断面、冠状面及矢状面图像)，表征所述目标对象在三维空间中的信息(例如，位置和尺寸等)。所述MRI图像提供的目标对象在三维空间中的信息可以用于治疗前对LITT探针、OCT探针和/或测温元件经过人体组织到达所述目标对象处的路径进行规划(简称入针规划)。所述MRI图像提供的目标对象在三维空间中的信息也可以用于治疗过程中引导所述LITT探针、OCT探针和/或测温元件按照规划的路径进入人体组织，并到达所述目标对象处(简称入针引导)。在一些实施例中，所述MRI图像可以显示于终端209。用户，如医生，可以通过终端209(例如，终端209上的触摸屏、鼠标、键盘等物理元件)，基于所述MRI图像，进行LITT探针的入针规划和入针引导。在一些实施例中，系统也可以自动基于所述MRI图像，进行LITT探针的入针规划和入针引导。The MRI device 202 is used to image a specific area including a target object (e.g., a tumor in the patient's brain) to generate an MRI image. The MRI image may be a real-time MRI image or a non-real-time MRI image. The MRI image may include a three-dimensional image or multiple two-dimensional images (e.g., cross-sectional, coronal, and sagittal images) to characterize information about the target object in three-dimensional space (e.g., position and size, etc.). The information about the target object in three-dimensional space provided by the MRI image can be used to plan the path for the LITT probe, OCT probe, and/or temperature measuring element to pass through human tissue to reach the target object before treatment (referred to as needle insertion planning). The information about the target object in three-dimensional space provided by the MRI image can also be used to guide the LITT probe, OCT probe, and/or temperature measuring element to enter human tissue along the planned path and reach the target object during treatment (referred to as needle insertion guidance). In some embodiments, the MRI image may be displayed on the terminal 209. A user, such as a doctor, can perform needle insertion planning and needle insertion guidance of the LITT probe based on the MRI image through the terminal 209 (e.g., physical elements such as a touch screen, mouse, and keyboard on the terminal 209). In some embodiments, the system may also automatically perform needle insertion planning and guidance of the LITT probe based on the MRI image.
在一些实施例中，MRI设备202还可以对包括所述目标对象的特定区域进行磁共振热成像，生成热图像。所述热图像可以与所述MRI图像进行配准，同时表示所述包含目标对象的特定区域的解剖结构信息以及相应位置的温度变化信息。头部线圈203用于提供较深度的头部MRI信号。在一些实施例中，头部线圈203为霍姆赫兹磁性线圈。当所述目标对象(例如，肿瘤)处于患者脑部时，头部线圈203可以发射RF信号，并接收头部MRI信号。所述头部线圈203采集的头部MRI信号相比于MRI设备202采集的MRI信号具有更高的信噪比(SNR)。因此，基于头部线圈203采集的头部MRI信号重建的头部MRI图像中，所述目标对象的信息更加精确。在本申请中，头部线圈203通过可以通过接口耦合至MRI设备202，以生成更加精确的头部MRI图像。In some embodiments, the MRI device 202 can also perform magnetic resonance thermography on a specific area including the target object to generate a thermal image. The thermal image can be registered with the MRI image, and simultaneously represents the anatomical structure information of the specific area containing the target object and the temperature change information of the corresponding location. The head coil 203 is used to provide deeper head MRI signals. In some embodiments, head coil 203 is a Holmhertz magnetic coil. When the target object (eg, a tumor) is in the patient's brain, the head coil 203 can transmit RF signals and receive head MRI signals. The head MRI signal collected by the head coil 203 has a higher signal-to-noise ratio (SNR) than the MRI signal collected by the MRI device 202 . Therefore, in the head MRI image reconstructed based on the head MRI signal collected by the head coil 203, the information of the target object is more accurate. In this application, the head coil 203 may be coupled to the MRI device 202 through an interface to generate more accurate head MRI images.
在一些实施例中，头部线圈203可以获取头部热图像数据，用于头部MRTI。基于所述头部热图像数据，可以重建患者头部热图像。在一些实施例中，头部线圈203也可以对患者头部进行支撑固定。In some embodiments, head coil 203 can acquire head thermal image data for head MRTI. Based on the head thermal image data, a thermal image of the patient's head can be reconstructed. In some embodiments, the head coil 203 can also support and fixate the patient's head.
LITT设备用于产生激光，并利用激光的热效应，对目标对象进行治疗。LITT设备包括激光器，LITT探针(例如，LITT侧向消融探针、LITT周向消融探针)，以及连接所述激光器与所述LITT探针的通道(如光纤)及接口。在一些实施例中，所述激光器可以包括可调谐激光二极管和/或不可调谐激光二极管。所述可调谐激光二极管的激光功率在特定范围内，例如，0W-500W，10-250W，50-150W等，可调谐。所述不可调谐激光二极管的激光功率为特定数值，例如，10W，12W，15W，20W，30W，60W，100W，150W等。LITT equipment is used to generate laser light and use the thermal effect of the laser to treat the target object. The LITT device includes a laser, a LITT probe (eg, a LITT lateral ablation probe, a LITT circumferential ablation probe), and a channel (such as an optical fiber) and interface connecting the laser and the LITT probe. In some embodiments, the laser may include a tunable laser diode and/or a non-tunable laser diode. The laser power of the tunable laser diode is tunable within a specific range, for example, 0W-500W, 10-250W, 50-150W, etc. The laser power of the non-tunable laser diode is a specific value, for example, 10W, 12W, 15W, 20W, 30W, 60W, 100W, 150W, etc.
在一些实施例中，LITT设备包括LITT探针位移控制器210，用于控制LITT探针的位移。在对目标对象治疗时，LITT探针位移控制器210控制LITT探针经由接口平台206上固定设置的入针通道，穿过患者头骨，进入其颅内，根据入针规划和入针指引，到达所述目标对象所在位置。其中，接口平台206固定到患者头部。在一些实施例中，医学治疗装置200可以包括位移传感器(图中未示出)，用于实时反馈LITT探针的在入针过程中的位移数据。所述位移传感器可以为，例如，压电传感器、电感式传感器、涡流传感器等。所述位移传感器可以连接于所述LITT探针。所述位移传感器可以设置于接口平台206。In some embodiments, the LITT device includes a LITT probe displacement controller 210 for controlling the displacement of the LITT probe. When treating the target object, the LITT probe displacement controller 210 controls the LITT probe to pass through the needle insertion channel fixedly provided on the interface platform 206, pass through the patient's skull, enter the skull, and reach the target according to the needle insertion planning and needle insertion guidance. The location of the target object. Among them, the interface platform 206 is fixed to the patient's head. In some embodiments, the medical treatment device 200 may include a displacement sensor (not shown in the figure) for real-time feedback of displacement data of the LITT probe during the needle insertion process. The displacement sensor may be, for example, a piezoelectric sensor, an inductive sensor, an eddy current sensor, etc. The displacement sensor may be connected to the LITT probe. The displacement sensor may be disposed on the interface platform 206 .
在一些实施例中，激光器发出的激光，经光路中继处理装置211处理后，传输至LITT探针。所述光路中继 处理装置211可以对所述激光的参数(例如，功率、频率等)进行调整。例如，所述光路中继处理装置211可以补偿激光的衰减，使其达到特定的功率，或对激光进行衰减处理，使其功率满足治疗的需要。所述光路中继处理装置211设置于控制中继平台204。In some embodiments, the laser light emitted by the laser is processed by the optical path relay processing device 211 and then transmitted to the LITT probe. The optical path relay processing device 211 can adjust the parameters of the laser (for example, power, frequency, etc.). For example, the optical path relay processing device 211 can compensate for the attenuation of the laser so that it reaches a specific power, or perform attenuation processing on the laser so that its power meets the needs of treatment. The optical path relay processing device 211 is provided on the control relay platform 204 .
OCT设备基于生物结构的透光性，探测生物组织的反射、散射等信号，并将其转换成电信号，生成OCT图像。所述OCT图像为实时OCT图像，也可以是非实时OCT图像。OCT设备包括光源、OCT探针、干涉部件以及连接各部件的光纤及接口。所述光源采用低相干光源，以提高成像的纵向分辨率。所述OCT探针的示例性结构可以参照本申请其他附图(例如，图15)及其描述，此处不再赘述。Based on the light transmittance of biological structures, the OCT device detects the reflection, scattering and other signals of biological tissues, converts them into electrical signals, and generates OCT images. The OCT image is a real-time OCT image, and can also be a non-real-time OCT image. The OCT device includes a light source, an OCT probe, an interference component, and optical fibers and interfaces connecting the components. The light source uses a low-coherence light source to improve the longitudinal resolution of imaging. The exemplary structure of the OCT probe can refer to other drawings (e.g., Figure 15) and their descriptions in this application, and will not be repeated here.
在本实施例中，所述OCT设备可以是双模OCT，其光源可以产生两种不同参数(带宽、中央波长)的光信号。示例性地，双模OCT采用超过160nm带宽840nm中央波长，以及超过100nm扫频范围1300nm中央波长的光信号。双模OCT可以提供接近1μm分辨率、cm级深度的病理成像。In this embodiment, the OCT device may be a dual-mode OCT, and its light source may generate optical signals with two different parameters (bandwidth, central wavelength). Illustratively, the dual-mode OCT uses an optical signal with a central wavelength of 840 nm over a 160 nm bandwidth, and a central wavelength of 1300 nm over a 100 nm sweep range. Dual-mode OCT can provide pathological imaging with a resolution close to 1 μm and a depth of cm.
在OCT设备产生的光信号的传播路径(例如，旋转接头处)上，可以采用光纤滑环装置212，以保证光信号的不间断传输。对于双模OCT，可以采用多通道光纤滑环装置(如双通道光纤滑环装置，以适配上述两种不同中央波长的光信号)，也称为多模光纤滑环装置。光纤滑环装置212可以设置于控制中继平台204。On the propagation path of the optical signal generated by the OCT equipment (for example, at the rotary joint), the optical fiber slip ring device 212 can be used to ensure uninterrupted transmission of the optical signal. For dual-mode OCT, a multi-channel optical fiber slip ring device can be used (such as a dual-channel optical fiber slip ring device to adapt to the above-mentioned two optical signals with different central wavelengths), also called a multi-mode optical fiber slip ring device. The optical fiber slip ring device 212 may be disposed on the control relay platform 204 .
测温元件用于对所述目标对象或其周边组织和/或LITT探针进行测温。测温元件可以包括热电偶(如K型热电偶)、FBG传感器等。The temperature measuring element is used to measure the temperature of the target object or its surrounding tissue and/or the LITT probe. Temperature measuring elements can include thermocouples (such as K-type thermocouples), FBG sensors, etc.
所述FBG传感器，使用特殊制备的原材料制备而得到。该原材料须满足特定的参数条件。示例性地，所述参数条件包括：材料截止波长≤1280nm，1310nm时最大衰减标准取样≤0.35dB/km，1625nm时最大衰减标准取样≤0.23dB/km，1310nm时光纤模场直径(MFD)模式场外径＝9.2±0.4μm，1550nm时MFD模式场外径＝10.4±0.5μm，1550nm时色散≤18ps/(nm.km)，1625nm时色散≤22ps/(nm.km)，偏振模式色散LDV≤0.06，最大分隔纤维≤0.1，1310nm和1550nm时点不连续性≤0.05dB，包层外径＝125±0.3μm，芯包同心度≤0.3μm，包层失圆性≤0.7％，芯径＝8.2μm，叠加丙烯酸酯涂层外径＝242±5μm，涂覆包层同心度＜12μm，着色CD＝250+15/-9μm，纤维卷曲≥5曲率半径m，数值孔径0.12，折射率差0.36％，1310nm时有效折射率群1.467，1550nm时有效折射率群1.4677，抗疲劳性参数＝20，1310nm时瑞丽背向散射系数-77dB，1550nm时瑞丽背向散射系数-82dB。同时，该材料另须满足特殊色散公式D(λ)：The FBG sensor is prepared using specially prepared raw materials. The raw material must meet certain parameters. Exemplarily, the parameter conditions include: material cutoff wavelength ≤ 1280nm, maximum attenuation standard sampling at 1310nm ≤ 0.35dB/km, maximum attenuation standard sampling at 1625nm ≤ 0.23dB/km, fiber mode field diameter (MFD) mode at 1310nm Field outer diameter=9.2±0.4μm, MFD mode field outer diameter=10.4±0.5μm at 1550nm, dispersion ≤18ps/(nm.km) at 1550nm, dispersion ≤22ps/(nm.km) at 1625nm, polarization mode dispersion LDV ≤0.06, maximum separation fiber ≤0.1, point discontinuity at 1310nm and 1550nm ≤0.05dB, cladding outer diameter=125±0.3μm, core-pack concentricity ≤0.3μm, cladding out-of-roundness ≤0.7%, core diameter =8.2μm, superimposed acrylic coating outer diameter=242±5μm, coating concentricity <12μm, coloring CD=250+15/-9μm, fiber curl ≥5 radius of curvature m, numerical aperture 0.12, refractive index difference 0.36%, effective refractive index group at 1310nm is 1.467, effective refractive index group at 1550nm is 1.4677, fatigue resistance parameter = 20, Ruili backscattering coefficient at 1310nm -77dB, Ruili backscattering coefficient at 1550nm -82dB. At the same time, the material must also satisfy the special dispersion formula D(λ):
Figure PCTCN2022123856-appb-000001
其中1200nm≤λ≤1625nm、S 0零色散斜率≤0.088ps/(nm 2，km)、λ 0零色散波长1304nm≤λ 0≤1324nm。
Figure PCTCN2022123856-appb-000001
Among them, 1200nm≤λ≤1625nm, S 0 zero dispersion slope ≤0.088ps/(nm 2 , km), λ 0 zero dispersion wavelength 1304nm≤λ 0 ≤1324nm.
上述原材料经过特定波长范围(例如，240-244nm，244-248nm，248-252nm，252-256nm等)的紫外光照射，使得光纤芯的折射率得到周期性调制。周期性的核心索引调制产生核心模式，这些模式通过众多的索引边界反射或传输，并相互干扰。反过来，输入光束只在由一定相位匹配条件决定的特定波长处经历强反射，反射波长被称为FBG的布拉格波长，相位匹配条件，称为布拉格条件，最终形成FBG传感器。所述FBG传感器可用于实时监测激光消融弥散辐照期间的间质组织(例如，目标对象及其周边组织)和LITT探针(远端)温度。所述FBG传感器的具体制备可以参照本申请其他附图(例如，图16)及其描述，此处不再赘述。The above-mentioned raw materials are irradiated with ultraviolet light in a specific wavelength range (for example, 240-244nm, 244-248nm, 248-252nm, 252-256nm, etc.), so that the refractive index of the optical fiber core is periodically modulated. Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other. In turn, the input beam only experiences strong reflection at specific wavelengths determined by certain phase matching conditions. The reflected wavelength is called the Bragg wavelength of the FBG. The phase matching condition, called the Bragg condition, ultimately forms the FBG sensor. The FBG sensor can be used for real-time monitoring of interstitial tissue (eg, target object and its surrounding tissue) and LITT probe (distal) temperature during diffuse laser ablation irradiation. For the specific preparation of the FBG sensor, reference can be made to other drawings of this application (for example, Figure 16) and their descriptions, and will not be described again here.
冷却设备用于对控制LITT探针的温度。由于LITT探针是通过发出激光，利用激光的热效应，治疗目标物体，因此，在治疗过程中LITT探针的温度会随着治疗时间的延长而升高。过高的温度不仅会影响探针的正常工作，而且会损伤正常人体组织，可能形成术后后遗症。当LITT探针的温度过高时，冷却设备经冷却通道214将特定冷却媒介(例如，CO 2气体)输送至LITT探针远端，对LITT探针进行降温。冷却设备包括冷却源(未示出)、冷却控制元件213和冷却通道214。冷却源用于存储冷却媒介。示例性地，所述冷却媒介可以为CO 2气体。所述冷却源可以是CO 2气源气罐，用于存储CO 2气体。冷却控制元件213可以控制冷却源的开、关，以及冷却媒介的参数(例如，CO 2气体的流速、压力)等。 Cooling equipment is used to control the temperature of the LITT probe. Since the LITT probe emits laser light and uses the thermal effect of the laser to treat the target object, the temperature of the LITT probe will increase as the treatment time increases during the treatment process. Excessive temperature will not only affect the normal operation of the probe, but also damage normal human tissues and may cause postoperative sequelae. When the temperature of the LITT probe is too high, the cooling device delivers a specific cooling medium (for example, CO 2 gas) to the distal end of the LITT probe through the cooling channel 214 to cool down the LITT probe. The cooling device includes a cooling source (not shown), a cooling control element 213 and a cooling channel 214 . The cooling source is used to store the cooling medium. Exemplarily, the cooling medium may be CO2 gas. The cooling source may be a CO2 gas source tank for storing CO2 gas. The cooling control element 213 can control the on and off of the cooling source, as well as the parameters of the cooling medium (for example, the flow rate and pressure of CO 2 gas), etc.
在一些实施例中，可以将上述LITT探针、OCT探针、测温元件和/或冷却通道可以集成于一体，形成诊断治 疗一体化的集成探针224(后续简称为集成探针224)。例如，上述测温元件与LITT探针可以集成于一体，形成集成探针224。又例如，上述OCT探针可以与测温元件和LITT探针可以集成于一体，形成集成探针224。又例如，上述LITT探针、OCT探针、测温元件和冷却通道可以集成于一体，形成集成探针224。In some embodiments, the above-mentioned LITT probe, OCT probe, temperature measurement element and/or cooling channel can be integrated into one body to form an integrated probe 224 that integrates diagnosis and treatment (hereinafter referred to as integrated probe 224). For example, the temperature measuring element and the LITT probe can be integrated into one body to form the integrated probe 224 . For another example, the above-mentioned OCT probe can be integrated with the temperature measurement element and the LITT probe to form an integrated probe 224 . For another example, the above-mentioned LITT probe, OCT probe, temperature measurement element and cooling channel can be integrated into one body to form the integrated probe 224 .
驱动装置204用于驱动LITT探针(例如，集成探针224)运动，以到达所述目标对象所在位置(入针)或远离所述目标对象所在位置(回撤)。所述运动可以包括线性平移运动和旋转运动。在一些实施例中，驱动装置204包括驱动马达、线缆以及运动控制机构。所述LITT探针物理连接于所述运动控制机构。通过所述线缆和运动控制机构，可以将驱动马达输出的力传递至所述集成探针224，以控制其运动。在本实施例中，如图2B所示，所述线缆包括平移线缆215和旋转线缆216。相应地，所述运动控制机构包括平移控制机构217和旋转控制机构218。所述平移控制机构217用于控制所述集成探针224的平移运动。所述旋转控制机构218用于控制所述集成探针224的旋转运动。平移线缆215和旋转线缆216分别与平移控制机构217和旋转控制机构218连接。在一些实施例中，所述线缆(如平移线缆215和旋转线缆216)为特指丝线，具有较高刚性、较低的弹性模量，可实时1:1完成扭矩传输，以确保驱动LITT探针运动的准确性。The drive device 204 is used to drive the LITT probe (e.g., the integrated probe 224) to move to reach the location of the target object (needle insertion) or away from the location of the target object (withdrawal). The movement may include linear translation and rotation. In some embodiments, the drive device 204 includes a drive motor, a cable, and a motion control mechanism. The LITT probe is physically connected to the motion control mechanism. Through the cable and the motion control mechanism, the force output by the drive motor can be transmitted to the integrated probe 224 to control its movement. In this embodiment, as shown in Figure 2B, the cable includes a translation cable 215 and a rotation cable 216. Accordingly, the motion control mechanism includes a translation control mechanism 217 and a rotation control mechanism 218. The translation control mechanism 217 is used to control the translation movement of the integrated probe 224. The rotation control mechanism 218 is used to control the rotation movement of the integrated probe 224. The translation cable 215 and the rotation cable 216 are connected to the translation control mechanism 217 and the rotation control mechanism 218, respectively. In some embodiments, the cables (such as the translation cable 215 and the rotation cable 216) are specific silk threads with high rigidity and low elastic modulus, and can complete torque transmission in real time 1:1 to ensure the accuracy of driving the LITT probe movement.
所述驱动马达可以根据需求，带动平移线缆215和/或旋转线缆216运动，经由所述平移控制机构217和/或旋转控制机构218，控制所述集成探针224的平移和/或旋转运动，实现所述LITT探针(或集成探针224)两个自由度的精确运动控制。在一些实施例中，所述平移控制机构217和旋转控制机构218可以设置于接口平台205。关于驱动装置204的具体结构及工作原理，可以参照本申请中其他附图(例如，图3和图4)及其描述，此处不再赘述。The drive motor can drive the translation cable 215 and/or the rotation cable 216 to move as required, and control the translation and/or rotation of the integrated probe 224 via the translation control mechanism 217 and/or the rotation control mechanism 218. Movement to achieve precise motion control of the two degrees of freedom of the LITT probe (or integrated probe 224). In some embodiments, the translation control mechanism 217 and the rotation control mechanism 218 may be provided on the interface platform 205 . Regarding the specific structure and working principle of the driving device 204, reference may be made to other drawings in this application (for example, FIG. 3 and FIG. 4) and their descriptions, which will not be described again here.
接口平台205可以搭载医学治疗装置200的一个或多个部件或元件。示例性地，搭载的部件或元件包括上述LITT探针的入针通道，位移传感器，运动控制机构(如平移控制机构217和旋转控制机构218)等。在一些实施例中，接口平台205可以是双轴立体框架，如图中所示。接口平台205可以固定到患者头部(颅骨)，与患者头部保持稳定连接，不发生相对位移。接口平台205搭载的部件或元件可以固定连接于所述双轴立体框架。LITT探针(上述集成探针224)可以通过接口平台205提供的入针通道经入针规划路径进入患者颅内，准确地到达目标对象所在位置。 Interface platform 205 may carry one or more components or elements of medical treatment device 200 . Exemplarily, the mounted components or elements include the needle entry channel of the LITT probe, a displacement sensor, a motion control mechanism (such as a translation control mechanism 217 and a rotation control mechanism 218), etc. In some embodiments, interface platform 205 may be a biaxial stereoscopic frame, as shown in the figure. The interface platform 205 can be fixed to the patient's head (skull) and maintain a stable connection with the patient's head without relative displacement. The components or elements carried by the interface platform 205 can be fixedly connected to the biaxial three-dimensional frame. The LITT probe (the above-mentioned integrated probe 224) can enter the patient's skull through the needle insertion channel provided by the interface platform 205 through the needle insertion path, and accurately reach the location of the target object.
控制中继平台206集成了医学治疗装置200的一个或多个部件或元件的中段或中继控制。示例性地，控制中继平台206集成了上述LITT探针位移控制器210、光路中继处理装置211、OCT光纤滑环212、冷却控制元件213、以及驱动装置204的部分构件，如驱动马达。 Control relay platform 206 integrates mid-stage or relay control of one or more components or elements of medical treatment device 200 . For example, the control relay platform 206 integrates the above-mentioned LITT probe displacement controller 210, optical path relay processing device 211, OCT optical fiber slip ring 212, cooling control element 213, and some components of the driving device 204, such as a driving motor.
如图2C所示，控制中继平台206上设置有封装盒。LITT探针位移控制器210、光路中继处理装置211、OCT光纤滑环212、冷却控制元件213设置于封装盒中。As shown in Figure 2C, a packaging box is provided on the control relay platform 206. The LITT probe displacement controller 210, the optical path relay processing device 211, the OCT optical fiber slip ring 212, and the cooling control element 213 are arranged in the packaging box.
如图所示，封装盒中引出了5个通道，包括OCT探针通道219(光纤)、LITT探针通道220(光纤)、冷却通道214、测温元件控制线缆通道221以及位移传感器线缆通道222。其中，OCT光纤滑环212连接OCT探针通道219；光路中继处理装置211连接LITT探针通道220和测温元件控制线缆通道221；冷却控制元件213连接冷却通道214；LITT探针位移控制器210连接位移传感器线缆通道222。As shown in the figure, 5 channels are introduced in the packaging box, including OCT probe channel 219 (optical fiber), LITT probe channel 220 (optical fiber), cooling channel 214, temperature measurement element control cable channel 221 and displacement sensor cable Channel 222. Among them, the OCT optical fiber slip ring 212 is connected to the OCT probe channel 219; the optical path relay processing device 211 is connected to the LITT probe channel 220 and the temperature measurement element control cable channel 221; the cooling control element 213 is connected to the cooling channel 214; the LITT probe displacement control The connector 210 is connected to the displacement sensor cable channel 222.
集成元件207用于对医学治疗装置200的信号控制线缆、光学通道、冷却通道等进行集成。在一些实施例中，如图2D所示，集成元件207可以将OCT探针通道219、LITT探针通道220、冷却通道214以及测温元件控制线缆通道221等进行整合集成，例如，机械耦合。集成元件207包括集成管路223，可以容纳OCT探针通道219、LITT探针通道220、冷却通道214、和测温元件控制线缆通道221。所述集成管路223可以连接所述集成探针224，例如，密封连接于所述集成探针224的外壳。通过集成元件207对医学治疗装置200的信号控制线缆、光学通道、冷却通道等进行集成，可以优化管线传输效率，提高整个医学治疗装置200运行的稳定性。The integrated component 207 is used to integrate signal control cables, optical channels, cooling channels, etc. of the medical treatment device 200 . In some embodiments, as shown in Figure 2D, the integrated component 207 can integrate the OCT probe channel 219, the LITT probe channel 220, the cooling channel 214 and the temperature measurement element control cable channel 221, etc., for example, mechanical coupling . The integrated component 207 includes an integrated pipeline 223 that can accommodate an OCT probe channel 219, a LITT probe channel 220, a cooling channel 214, and a temperature measuring element control cable channel 221. The integrated pipeline 223 may be connected to the integrated probe 224 , for example, sealingly connected to the housing of the integrated probe 224 . By integrating the signal control cables, optical channels, cooling channels, etc. of the medical treatment device 200 through the integrated component 207 , the pipeline transmission efficiency can be optimized and the operation stability of the entire medical treatment device 200 can be improved.
控制设备208可以用于对医学治疗装置200的一个或多个部件进行控制，执行相应的操作。控制设备208可以基于控制的部件及需要执行的操作，生成相应的指令。所述指令以电信号的形式，传达至对应的部件，使该部件执行相应的操作。在一些实施例中，控制设备208集成有OCT成像控制模块、LITT治疗控制模块、测温元件温 控模块、头部线圈成像配准模块、冷却系统控制模块、LITT探针位置传感控制模块、驱动控制模块、支撑固定平台控制模块等。关于控制设备208的具体模块及功能，可以参照本申请中其他附图(例如，图5)及其描述，此处不再赘述。The control device 208 may be used to control one or more components of the medical treatment device 200 and perform corresponding operations. The control device 208 can generate corresponding instructions based on the components being controlled and the operations that need to be performed. The instructions are conveyed to the corresponding component in the form of electrical signals, causing the component to perform corresponding operations. In some embodiments, the control device 208 integrates an OCT imaging control module, a LITT treatment control module, a temperature measurement element temperature control module, a head coil imaging registration module, a cooling system control module, and a LITT probe position sensing control module. Drive control module, support fixed platform control module, etc. Regarding the specific modules and functions of the control device 208, reference may be made to other drawings (for example, FIG. 5) and their descriptions in this application, which will not be described again here.
终端209可以对医学治疗装置200中各部件及患者相关的信息以图像、数据等形式进行显示。示例性地，终端209可以显示目标对象的MRI图像、热图像、MRI图像与热图像的配准图像、OCT图像、测温元件测得的温度信息以及冷却设备对LITT探针的冷却信息。在一些实施例中，终端209也可以接收用户输入的信息。通过终端209输入的信息可以包括图像、数字、文本、语音等。例如，用户可以通过终端209输入一个或多个操作指令。所述操作指令可以包括调整患者体位布局的指令，MRI设备202，头部线圈203，LITT设备(如LITT探针)，OCT设备(如OCT探针)，冷却设备等的工作模式/参数设置指令，治疗时LITT探针入针路径规划指令等。通过终端209输入的信息可以被发送至控制设备208。控制设备208可以生成控制指令，以控制相应的设备或部件执行相应的操作。在一些实施例中，终端209可以是或包括，如计算机、手机、平板电脑、控制台等。The terminal 209 can display information related to each component in the medical treatment device 200 and the patient in the form of images, data, etc. For example, the terminal 209 can display the MRI image of the target object, the thermal image, the registration image of the MRI image and the thermal image, the OCT image, the temperature information measured by the temperature measurement element, and the cooling information of the LITT probe by the cooling device. In some embodiments, terminal 209 may also receive user-entered information. Information input through the terminal 209 may include images, numbers, text, voice, etc. For example, the user can input one or more operation instructions through the terminal 209. The operation instructions may include instructions for adjusting the patient's body position layout, operating mode/parameter setting instructions for the MRI equipment 202, head coil 203, LITT equipment (such as LITT probe), OCT equipment (such as OCT probe), cooling equipment, etc. , LITT probe needle path planning instructions during treatment, etc. Information entered via terminal 209 may be sent to control device 208 . The control device 208 can generate control instructions to control the corresponding device or component to perform corresponding operations. In some embodiments, the terminal 209 may be or include a computer, a mobile phone, a tablet, a console, etc.
所有以上构件是MRI可兼容的，这指的是组件在MRI环境中使用的能力。在一定磁通密度下，MRI可兼容组件操作不会对MRI产生显著的干扰，例如，对于特定的环境(例如，0.5T、0.75T、1T、1.5T、2.0T、3.0T等)，以上构件的操作没有危险。All of the above components are MRI compatible, which refers to the component's ability to be used in an MRI environment. Under a certain magnetic flux density, the operation of MRI-compatible components will not cause significant interference to MRI. For example, for specific environments (for example, 0.5T, 0.75T, 1T, 1.5T, 2.0T, 3.0T, etc.), the above There is no danger in the operation of the components.
图3A和3B是根据本说明书一些实施例的示例性驱动装置的结构示意图。3A and 3B are structural schematic diagrams of an exemplary driving device according to some embodiments of this specification.
如图3A所示，驱动装置300包括动力输入端301，线缆302和303，以及动力输出端304。动力输出端304连接LITT探针(或集成探针224)。动力输入端301输入的动力可以通过传递至动力输出端304，驱动LITT探头(或集成探针224)运动。动力输出端301可以为驱动马达。线缆302和303分别为平移线缆和旋转线缆，分别控制LITT探针(或集成探针224)的平移运动和旋转运动。As shown in FIG. 3A , the driving device 300 includes a power input terminal 301 , cables 302 and 303 , and a power output terminal 304 . The power output 304 is connected to the LITT probe (or integrated probe 224). The power input from the power input terminal 301 can be transmitted to the power output terminal 304 to drive the LITT probe (or integrated probe 224) to move. The power output end 301 may be a driving motor. Cables 302 and 303 are respectively translation cables and rotation cables, respectively controlling the translation movement and rotation movement of the LITT probe (or integrated probe 224).
与图2A-2D不同的是，驱动装置300额外包括驱动旋钮305和306。如图3B所示，驱动旋钮305和线缆303之间通过两个啮合的锥齿轮307和308连接。两个啮合的锥齿轮307和308构成锥齿轮传动机构，因此通过旋转驱动旋钮305，也可以带动线缆303运动，从而控制LITT探针(或集成探针224)的运动(例如，旋转运动)。通过啮合的锥齿轮307和308，可以完成扭矩增大与传输，从而实现驱动旋钮305上较小的驱动力矩即可带动线缆303运动。类似地，驱动旋钮306和线缆302之间也通过两个啮合的锥齿轮连接。在一些实施例中，可以手动控制驱动旋钮305和306，分别带动线缆303和302运动，从而控制LITT探针(或集成探针224)的运动，作为对马达驱动方式的补充，同时，也具有更好的灵活性。Different from FIGS. 2A-2D , the driving device 300 additionally includes driving knobs 305 and 306 . As shown in Figure 3B, the drive knob 305 and the cable 303 are connected through two meshed bevel gears 307 and 308. Two meshed bevel gears 307 and 308 constitute a bevel gear transmission mechanism. Therefore, by rotating the drive knob 305, the cable 303 can also be driven to move, thereby controlling the movement (for example, rotational movement) of the LITT probe (or integrated probe 224). . Through the meshing bevel gears 307 and 308, the torque can be increased and transmitted, so that a smaller driving torque on the driving knob 305 can drive the movement of the cable 303. Similarly, the drive knob 306 and the cable 302 are also connected through two meshing bevel gears. In some embodiments, the driving knobs 305 and 306 can be manually controlled to drive the movement of the cables 303 and 302 respectively, thereby controlling the movement of the LITT probe (or integrated probe 224) as a supplement to the motor driving method, and at the same time, Have better flexibility.
图4A-4C是根据本说明书一些实施例的示例性平移控制机构和/或旋转控制机构的结构示意图。4A-4C are structural schematic diagrams of exemplary translation control mechanisms and/or rotation control mechanisms according to some embodiments of this specification.
图中所示为不同视角下的动力输出端304。动力输出端304包括平移控制机构和旋转控制机构。平移控制机构和旋转控制机构分别直接控制LITT探针(或集成探针224)的平移运动和旋转运动。The figure shows the power output end 304 at different viewing angles. The power output end 304 includes a translation control mechanism and a rotation control mechanism. The translation control mechanism and the rotation control mechanism directly control the translation movement and rotation movement of the LITT probe (or integrated probe 224) respectively.
示例性地，旋转控制机构包括一组同步带传动组件403。同步带传动组件403连接LITT探针通道404和旋转线缆。LITT探针(或集成探针224)固定设置于LITT探针通道404。如图4A所示，旋转线缆的位移经中间元件(例如，锥齿轮组合、涡轮蜗杆组合)转换，带动同步带传动组件403转动，从而使得LITT探针(或集成探针224)旋转，由此同步带传动组件403通过特定的减速比完成一定转速下的LITT探针(或集成探针224)运动控制。Illustratively, the rotation control mechanism includes a set of timing belt drive assemblies 403 . The timing belt drive assembly 403 connects the LITT probe channel 404 and the rotation cable. The LITT probe (or integrated probe 224) is fixedly disposed in the LITT probe channel 404. As shown in FIG. 4A , the displacement of the rotating cable is converted by the intermediate element (for example, bevel gear combination, worm gear combination), driving the synchronous belt transmission assembly 403 to rotate, thereby causing the LITT probe (or integrated probe 224 ) to rotate. This synchronous belt transmission assembly 403 completes motion control of the LITT probe (or integrated probe 224) at a certain rotation speed through a specific reduction ratio.
平移控制机构包括蜗轮蜗杆组件401与同步带传动组件402。如图4B和4C所示，平移线缆的位移经蜗轮蜗杆组件401改变输入轴方位，传输至同步带传动组件402，实现LITT探针(或集成探针224)的平移。同时，还可以达到一定的自锁效果使得LITT探针(或集成探针224)更加稳定，不受外力干扰。在一些实施例中，平移控制机构和旋转控制机构也可以通过齿轮组传动机构实现。The translation control mechanism includes a worm gear assembly 401 and a synchronous belt transmission assembly 402. As shown in Figures 4B and 4C, the displacement of the translation cable changes the input shaft orientation through the worm gear assembly 401 and is transmitted to the synchronous belt transmission assembly 402 to realize translation of the LITT probe (or integrated probe 224). At the same time, a certain self-locking effect can also be achieved to make the LITT probe (or integrated probe 224) more stable and free from external force interference. In some embodiments, the translation control mechanism and the rotation control mechanism can also be implemented through a gear set transmission mechanism.
图5是根据本说明书一些实施例所示的控制设备的示例性结构图。Figure 5 is an exemplary structural diagram of a control device according to some embodiments of this specification.
如图所示，控制设备208包括OCT成像控制模块501、LITT治疗控制模块502、测温元件温控模块503、头部线圈成像配准模块504、冷却系统控制模块505、LITT探针位置传感控制模块506、驱动控制模块507和支撑固定平台控制模块508。As shown in the figure, the control device 208 includes an OCT imaging control module 501, a LITT treatment control module 502, a temperature measurement element temperature control module 503, a head coil imaging registration module 504, a cooling system control module 505, and a LITT probe position sensing module. Control module 506, drive control module 507 and support fixed platform control module 508.
结合图2A-2D，可知，OCT成像控制模块501用于控制OCT成像。OCT成像控制模块501可以通过生成指令，控制OCT设备发射光信号，设置成像的参数(例如，光信号带宽、光信号的中央波长、成像时间、图像对比度等)。在一些实施例中，OCT成像控制模块501还可以获取生成的病理诊断信号，以生成OCT图像。OCT设备发射的光信号经光纤滑环装置212，传输至OCT探针。Combined with Figures 2A-2D, it can be seen that the OCT imaging control module 501 is used to control OCT imaging. The OCT imaging control module 501 can control the OCT device to emit optical signals and set imaging parameters (for example, optical signal bandwidth, central wavelength of the optical signal, imaging time, image contrast, etc.) by generating instructions. In some embodiments, the OCT imaging control module 501 can also acquire the generated pathological diagnosis signal to generate an OCT image. The optical signal emitted by the OCT equipment is transmitted to the OCT probe through the optical fiber slip ring device 212.
LITT治疗控制模块502用于控制LITT探针对目标对象进行治疗。在一些实施例中，LITT治疗控制模块502集成有激光器控制器，可调谐激光二极管和/或不可调谐激光二极管。激光器控制器可以控制激光器(例如，所述可调谐激光二极管和/或不可调谐激光二极管)发射激光，为整个LITT提供消融能量源。LITT治疗控制模块502可以控制激光器发射激光，发出的激光经光路中继处理装置211，传输至LITT探针。The LITT treatment control module 502 is used to control the LITT probe to treat the target object. In some embodiments, LITT treatment control module 502 integrates a laser controller, a tunable laser diode and/or a non-tunable laser diode. The laser controller can control the laser (eg, the tunable laser diode and/or the non-tunable laser diode) to emit laser light to provide an ablation energy source for the entire LITT. The LITT treatment control module 502 can control the laser to emit laser, and the emitted laser is transmitted to the LITT probe through the optical path relay processing device 211.
测温元件温控模块503用于控制测温元件对目标对象及其周围组织和/或LITT探针进行测温。测温元件的测温信号(如FBG传感器热源光学信号或K型热电偶模电温控信号)，可以通过光路中继处理装置211传输。The temperature measurement element temperature control module 503 is used to control the temperature measurement element to measure the temperature of the target object and its surrounding tissues and/or the LITT probe. The temperature measurement signal of the temperature measurement element (such as the FBG sensor heat source optical signal or the K-type thermocouple analog temperature control signal) can be transmitted through the optical path relay processing device 211.
头部线圈成像配准模块504用于控制头部线圈的成像(如头部MRI图像、头部热图像)与MRI设备的成像(如MRI图像、热图像)进行配准，从而获得更清晰、准确且可以提供温度信息的图像。The head coil imaging registration module 504 is used to control the registration of the imaging of the head coil (such as head MRI image, head thermal image) and the imaging of the MRI equipment (such as MRI image, thermal image), so as to obtain clearer, Images that are accurate and provide temperature information.
冷却系统控制模块505用于控制冷却设备对LITT探针进行冷却。冷却系统控制模块505可以通过冷却控制元件213，对冷却源的开、关，以及冷却媒介的参数(例如，CO 2气体的流速、压力)进行控制，结合测温元件测得的LITT探头的温度，对LITT探头温度进行控制，防止探头发生过热而损坏，起到保护探头的作用。在一些实施例中，也可以结合测温元件测得的目标对象及其周边组织的温度，控制所述目标对象周边健康组织的温度，避免造成不必要的伤害。同时，冷却系统控制模块505可以控制冷却媒介经冷却通道进行循环利用。 The cooling system control module 505 is used to control the cooling equipment to cool the LITT probe. The cooling system control module 505 can control the opening and closing of the cooling source and the parameters of the cooling medium (for example, the flow rate and pressure of CO 2 gas) through the cooling control element 213, combined with the temperature of the LITT probe measured by the temperature measuring element. , controls the temperature of the LITT probe to prevent the probe from overheating and damage, and plays a role in protecting the probe. In some embodiments, the temperature of the target object and its surrounding tissue measured by the temperature measuring element can also be combined to control the temperature of the healthy tissue surrounding the target object to avoid unnecessary damage. At the same time, the cooling system control module 505 can control the cooling medium to be recycled through the cooling channel.
LITT探针位置传感控制模块506用于通过控制LITT探针位移控制器210，实时检测LITT探针深入颅内的实时位置。LITT探针位置传感控制模块506也可以实时发送控制信号给LITT探针位移控制器210，下达位移触发指令和接受位置反馈处理信号。所述位移触发指令用于触发LITT探针位移控制器210控制LITT探针运动。所述位置反馈处理信号用于基于LITT探针的实时位置，判断并决策LITT探针后续的运动(例如，继续前进、调整方向、回撤等)。The LITT probe position sensing control module 506 is used to detect the real-time position of the LITT probe deep into the skull in real time by controlling the LITT probe displacement controller 210 . The LITT probe position sensing control module 506 can also send control signals to the LITT probe displacement controller 210 in real time, issue displacement triggering instructions and receive position feedback processing signals. The displacement triggering instruction is used to trigger the LITT probe displacement controller 210 to control the movement of the LITT probe. The position feedback processing signal is used to judge and decide the subsequent movement of the LITT probe (for example, continue to move forward, adjust direction, retreat, etc.) based on the real-time position of the LITT probe.
驱动控制模块507用于控制驱动装置204的驱动马达，以带动平移线缆215和/或旋转线缆216，经由所述平移控制机构217和/或旋转控制机构218，控制所述LITT探针(或集成探针224)的平移和/或旋转运动，实现所述LITT探针(或集成探针224)两个自由度的精确运动控制。The drive control module 507 is used to control the drive motor of the drive device 204 to drive the translation cable 215 and/or the rotation cable 216, and control the LITT probe ( Or the translational and/or rotational movement of the integrated probe 224), achieving precise motion control of the two degrees of freedom of the LITT probe (or the integrated probe 224).
支撑固定平台控制模块508用于控制支撑固定平台201运动。支撑固定平台控制模块508通过发出运动控制指令，控制控制支撑固定平台201进行运动(例如，平移、倾斜、旋转等)，以调整患者体位布局，为MRI提供更好的扫描位置基准。The support and fixed platform control module 508 is used to control the movement of the support and fixed platform 201 . The support and fixed platform control module 508 controls the movement of the support and fixed platform 201 (for example, translation, tilt, rotation, etc.) by issuing motion control instructions to adjust the patient's posture layout and provide a better scanning position reference for MRI.
图6是根据本说明书一些实施例的示例性两种不同类型的集成探针。Figure 6 is an illustration of two different types of integrated probes in accordance with some embodiments of the present specification.
如图6所示，集成探针224连接有OCT探针通道、LITT探针通道、冷却通道和测温元件控制线缆通道。上述四个通道通过集成元件207进行机械耦合，共同容纳于集成元件207的集成管路中。所述集成管路直接或通过接口连接于所述集成探针224。示例性地，集成管路通过接口601连接于所述集成探针224。所述接口601设置于接口平台205上。As shown in Figure 6, the integrated probe 224 is connected to an OCT probe channel, a LITT probe channel, a cooling channel and a temperature measurement element control cable channel. The above four channels are mechanically coupled through the integrated component 207 and are jointly accommodated in the integrated pipeline of the integrated component 207 . The integrated pipeline is connected to the integrated probe 224 directly or through an interface. For example, the integrated pipeline is connected to the integrated probe 224 through the interface 601 . The interface 601 is provided on the interface platform 205.
所述两种不同类型的集成探针可以包括LITT侧向消融集成探针610和LITT周向消融集成探针660。The two different types of integrated probes may include a LITT lateral ablation integrated probe 610 and a LITT circumferential ablation integrated probe 660.
如图所示，LITT侧向消融集成探针610，包括测温元件611、CO 2送气管612、LITT侧向消融探针613(也称为LITT侧向消融针芯)、OCT探针614、CO 2集气管615。其中，LITT侧向消融集成探针610中的LITT侧向消融探针613可以通过至少两种不同工艺制备。 As shown in the figure, the LITT lateral ablation integrated probe 610 includes a temperature measuring element 611, a CO2 gas supply tube 612, a LITT lateral ablation probe 613 (also called a LITT lateral ablation needle core), an OCT probe 614, and a CO2 gas collection tube 615. The LITT lateral ablation probe 613 in the LITT lateral ablation integrated probe 610 can be prepared by at least two different processes.
LITT周向消融集成探针660，包括测温元件661、CO 2送气管662、LITT周向消融探针663(也称为LITT周向消融针芯)、OCT探针664、CO 2集气管665。其中，LITT侧向消融集成探针610中的LITT周向消融探针663具体的结构及工艺可以参照本申请其他附图(例如，图9-11)及其描述。 The LITT circumferential ablation integrated probe 660 includes a temperature measurement element 661, a CO 2 air supply tube 662, a LITT circumferential ablation probe 663 (also called a LITT circumferential ablation needle core), an OCT probe 664, and a CO 2 air collecting tube 665 . For the specific structure and process of the LITT circumferential ablation probe 663 in the LITT lateral ablation integrated probe 610, please refer to other drawings of this application (for example, Figures 9-11) and their descriptions.
图7所示为根据本说明书一些实施例的通过第一种工艺制备的示例性LITT侧向消融探针。Figure 7 shows an exemplary LITT lateral ablation probe prepared by the first process according to some embodiments of the present specification.
如图7所示，LITT侧向消融探针700包括探针主体710，连接面720和镀层730。连接面720为主体710与镀层730之间的连接界面。As shown in FIG. 7 , the LITT lateral ablation probe 700 includes a probe body 710 , a connection surface 720 and a coating 730 . The connection surface 720 is the connection interface between the main body 710 and the plating layer 730 .
探针主体710呈圆柱体状。在一些实施例中，探针主体710的端部(远端)具有一定倾角(即探针主体710的端面与探针主体710的轴线呈一定夹角，所述夹角为0-90°，且不含该范围的端点)。探针主体710由针芯和位于针芯外周的硬质包层构成。所述针芯由纯二氧化硅材料制成。所述硬质包层由技术增强型包层二氧化硅(TECS)材料制成。The probe body 710 is cylindrical. In some embodiments, the end (distal end) of the probe body 710 has a certain inclination angle (that is, the end surface of the probe body 710 and the axis of the probe body 710 form a certain angle, and the included angle is 0-90°, and does not include the endpoints of the range). The probe body 710 is composed of a needle core and a hard cladding located on the outer periphery of the needle core. The needle core is made of pure silicon dioxide material. The hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
所述针芯的直径(外径)为，例如，550-650μm。在一些实施例中，针芯的直径(外径)为560μm。在一些实施例中，针芯的直径(外径)为570μm。在一些实施例中，针芯的直径(外径)为580μm。在一些实施例中，针芯的直径(外径)为590μm。在一些实施例中，针芯的直径(外径)为600μm。在一些实施例中，针芯的直径(外径)为610μm。在一些实施例中，针芯的直径(外径)为620μm。在一些实施例中，针芯的直径(外径)为630μm。在一些实施例中，针芯的直径(外径)为640μm。The diameter (outer diameter) of the needle core is, for example, 550-650 μm. In some embodiments, the diameter (outer diameter) of the needle core is 560 μm. In some embodiments, the diameter (outer diameter) of the needle core is 570 μm. In some embodiments, the diameter (outer diameter) of the needle core is 580 μm. In some embodiments, the diameter (outer diameter) of the needle core is 590 μm. In some embodiments, the diameter (outer diameter) of the needle core is 600 μm. In some embodiments, the diameter (outer diameter) of the needle core is 610 μm. In some embodiments, the diameter (outer diameter) of the needle core is 620 μm. In some embodiments, the diameter (outer diameter) of the needle core is 630 μm. In some embodiments, the diameter (outer diameter) of the needle core is 640 μm.
所述硬质包层的厚度为，例如，5-30μm。在一些实施例中，所述硬质包层的厚度为5μm。在一些实施例中，所述硬质包层的厚度为10μm。在一些实施例中，所述硬质包层的厚度为15μm。在一些实施例中，所述硬质包层的厚度为20μm。在一些实施例中，所述硬质包层的厚度为25μm。在一些实施例中，所述硬质包层的厚度为30μm。The thickness of the hard cladding is, for example, 5-30 μm. In some embodiments, the hard cladding layer has a thickness of 5 μm. In some embodiments, the hard cladding layer has a thickness of 10 μm. In some embodiments, the hard cladding has a thickness of 15 μm. In some embodiments, the hard cladding has a thickness of 20 μm. In some embodiments, the hard cladding has a thickness of 25 μm. In some embodiments, the hard cladding has a thickness of 30 μm.
连接面720采用特定精度(例如，0.1μm，0.5μm，1μm，2μm，3μm等)的金刚石膜，去除一定数值孔径(例如，0.35NA，0.36NA，0.37NA，0.38NA，0.39NA，0.4NA，0.41NA，0.42NA，0.43NA，0.44NA，0.45NA等)的特殊阶跃折射率多模材质纤芯，并在外围设置技术增强型包层二氧化硅(TECS)硬质包层作为主料。进而通过将特定成分的悬浮液，涂覆于二氧化硅胶体基膜表面，而形成全反射透镜光洁面。The connection surface 720 uses a diamond film with specific precision (for example, 0.1 μm, 0.5 μm, 1 μm, 2 μm, 3 μm, etc.), and removes a certain numerical aperture (for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA) , 0.41NA, 0.42NA, 0.43NA, 0.44NA, 0.45NA, etc.) special step refractive index multi-mode material core, and a technology-enhanced cladding silica (TECS) hard cladding is set on the periphery as the main material. Then, a suspension of specific components is coated on the surface of the silica colloidal base film to form a smooth surface of the total reflection lens.
示例性地，所述悬浮液包含合成无定形二氧化硅、H 2O以及丙烷-1,2-二醇。在一些实施例中，按质量分数，所述悬浮液包含10％-20％的合成无定形二氧化硅、20％-30％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、20％-30％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含30％-40％的合成无定形二氧化硅、20％-30％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、10％-20％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、30％-40％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、20％-30％的H 2O、35％-45％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、20％-30％的H 2O、55％-65％的(丙烷-1,2-二醇)。 Illustratively, the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol. In some embodiments, by mass fraction, the suspension contains 10%-20% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 30%-40% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 10%-20% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 30%-40% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 35%-45% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 55%-65% (propane-1,2 -diol).
在一些实施例中，镀层730采用贵金属靶材镀层。所述贵金属可以包括，例如，金、银和铂族金属。镀层730通过蒸发镀膜(例如，电阻加热蒸发镀膜、电子束加热蒸发镀膜、感应加热蒸发镀膜)、溅射镀膜(如磁控溅射镀膜)、离子镀膜的方式形成。在一些实施例中，镀层730通过在连接面720的表面进行磁控溅射镀膜形成。例如，镀层730可以为双层结构，下层(靠近连接面720)为通过磁控镀膜涂覆特定厚度(例如，60纳米(nm)，80nm，100nm，120nm，140nm)的纯银(例如，99.99％，99.999％，99.9999％或99.99999％的纯银)，上层(远离连接面720)为通过磁控镀膜涂覆特定厚度(例如，120nm，130nm，140nm，150nm，160nm，170nm，180nm)的一氧化硅保护层。又例如，镀层730可以为单层结构，通过磁控镀膜涂覆特定厚度(例如，60nm，80nm，100nm，120nm，140nm)的纯金(例如，99.99％，99.999％，99.9999％或99.99999％的纯金)而形成。In some embodiments, the plating layer 730 uses noble metal target plating. The precious metals may include, for example, gold, silver, and platinum group metals. The coating 730 is formed by evaporation coating (for example, resistance heating evaporation coating, electron beam heating evaporation coating, induction heating evaporation coating), sputtering coating (such as magnetron sputtering coating), or ion plating. In some embodiments, the coating layer 730 is formed by magnetron sputtering coating on the surface of the connection surface 720 . For example, the plating layer 730 can be a double-layer structure, and the lower layer (near the connection surface 720) is pure silver (for example, 99.99) coated with a specific thickness (for example, 60 nanometers (nm), 80 nm, 100 nm, 120 nm, 140 nm) through magnetron coating. %, 99.999%, 99.9999% or 99.99999% pure silver), the upper layer (away from the connection surface 720) is coated with a specific thickness (for example, 120nm, 130nm, 140nm, 150nm, 160nm, 170nm, 180nm) by magnetron coating. Silicon oxide protective layer. For another example, the plating layer 730 may have a single-layer structure, and is coated with pure gold (for example, 99.99%, 99.999%, 99.9999% or 99.99999%) of a specific thickness (for example, 60nm, 80nm, 100nm, 120nm, 140nm) through magnetron coating. pure gold).
在一些实施例中，所述镀层730与探针主体710的轴线呈一定角度。所述角度为，例如，35°、37°、39°、41°、43°、45°、47°、49°等。上述纯银与一氧化硅涂层方案，结合镀层730的角度，可使LITT高功率消融激光反射率效率高达87％。与使用全内反射(TIR，其要求抛光表面入射角超过临界角度约43.5°)行光束偏转相比，纯银涂层可以防止光束通过抛光表面泄漏，有助于在较宽的入射角(即低于TIR角度范围)兼容性和均匀聚焦点，反射率、光路偏折性能和稳定性比TIR得到较大提升。In some embodiments, the plating 730 is at an angle to the axis of the probe body 710 . The angles are, for example, 35°, 37°, 39°, 41°, 43°, 45°, 47°, 49°, etc. The above pure silver and silicon monoxide coating scheme, combined with the angle of the coating 730, can make the LITT high-power ablation laser reflectivity efficiency as high as 87%. Compared to linear beam deflection using total internal reflection (TIR), which requires the polished surface to have an incident angle exceeding the critical angle of about 43.5°, pure silver coating prevents beam leakage through the polished surface, helping to deflect the beam at wider incident angles (i.e. Lower than TIR angle range) compatibility and uniform focusing point, reflectivity, optical path deflection performance and stability are greatly improved compared to TIR.
在该工艺下，LITT侧向消融探针700，以发射角为81°左右的射束，均匀发射受控激光到目标对象，以实现病灶组织消融。Under this process, the LITT lateral ablation probe 700 uses a beam with an emission angle of about 81° to uniformly emit controlled laser light to the target object to achieve ablation of the lesion tissue.
相应地，LITT侧向消融探针700的制备工艺(即第一种工艺)包括如下步骤：Accordingly, the preparation process of the LITT lateral ablation probe 700 (i.e., the first process) includes the following steps:
步骤S7-1：将主体710端面进行光洁化。Step S7-1: Smooth the end surface of the main body 710.
此处主体710的端面是指主体710与镀层730之间的连接界面，即连接面720。采用特定精度的金刚石膜，去除一定数值孔径的特殊阶跃折射率多模材质纤芯，并在外围设置技术增强型包层二氧化硅(TECS)硬质包层作为主料。进而通过将特定成分的悬浮液，涂覆于二氧化硅胶体基膜表面，使探针主体710的端部形成光洁面。示例性地，所述悬浮液包含合成无定形二氧化硅、H 2O以及丙烷-1,2-二醇。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、20％-30％的H 2O、45％-55％的(丙烷-1,2-二醇)。 The end surface of the main body 710 here refers to the connection interface between the main body 710 and the plating layer 730, that is, the connection surface 720. A specific precision diamond film is used to remove the core of a special step refractive index multi-mode material with a certain numerical aperture, and a technology-enhanced cladding silica (TECS) hard cladding is set as the main material on the periphery. Furthermore, a suspension of specific components is applied to the surface of the silica colloidal base film to form a smooth surface at the end of the probe body 710 . Illustratively, the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol. In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
需要注意的是，探针主体710的端部(远端)具有一定倾角，即探针主体710的端面与探针主体710的轴线呈一定夹角。若探针主体710的端部没有倾角，即探针主体710的端面与探针主体710的轴线垂直，则还包括打磨步骤，通过打磨可以使探针主体710的端面与探针主体710的轴线呈一定夹角，所述夹角为0-90°，且不含该范围的端点。可以采用机械加工的方式，通过砂轮打磨所述端面。It should be noted that the end (distal end) of the probe body 710 has a certain inclination angle, that is, the end surface of the probe body 710 forms a certain angle with the axis of the probe body 710 . If the end of the probe body 710 has no inclination angle, that is, the end surface of the probe body 710 is perpendicular to the axis of the probe body 710, a grinding step is also included. By grinding, the end surface of the probe body 710 can be aligned with the axis of the probe body 710. It forms a certain included angle, and the included angle is 0-90°, and does not include the endpoint of this range. Mechanical processing can be used to grind the end surface with a grinding wheel.
步骤S7-2：对光洁化后的主体710端面进行镀层，形成LITT侧向消融探针700。Step S7-2: Coating the smoothed end surface of the main body 710 to form the LITT lateral ablation probe 700.
主体710的端面采用贵金属靶材进行镀层。在一些实施例中，镀层730通过在主体710的端面进行磁控溅射镀膜形成。镀层730可以为双层结构，此时，双层结构中的下层(靠近所述端面)为通过磁控镀膜涂覆特定厚度(例如，60纳米(nm)，80nm，100nm，120nm，140nm)的纯银(例如，99.99％，99.999％，99.9999％或99.99999％的纯银)，双层结构中的上层(远离所述端面)为通过磁控镀膜涂覆特定厚度(例如，120nm，130nm，140nm，150nm，160nm，170nm，180nm)的一氧化硅保护层。镀层730也可以为单层结构，此时，通过磁控镀膜涂覆特定厚度(例如，60nm，80nm，100nm，120nm，140nm)的纯金(例如，99.99％，99.999％，99.9999％或99.99999％的纯金)而形成。The end face of the main body 710 is plated with a noble metal target. In some embodiments, the coating 730 is formed by magnetron sputtering coating on the end face of the main body 710. The coating 730 can be a double-layer structure, in which case the lower layer (close to the end face) of the double-layer structure is pure silver (e.g., 99.99%, 99.999%, 99.9999% or 99.99999% pure silver) coated with a specific thickness (e.g., 60 nanometers (nm), 80nm, 100nm, 120nm, 140nm) by magnetron coating, and the upper layer (away from the end face) of the double-layer structure is a silicon monoxide protective layer coated with a specific thickness (e.g., 120nm, 130nm, 140nm, 150nm, 160nm, 170nm, 180nm) by magnetron coating. The coating 730 may also be a single-layer structure, in which case it is formed by magnetron coating a specific thickness (e.g., 60nm, 80nm, 100nm, 120nm, 140nm) of pure gold (e.g., 99.99%, 99.9999%, 99.9999% or 99.99999% pure gold).
图8所示为根据本说明书一些实施例的通过第二种工艺制备的示例性LITT侧向消融针芯。Figure 8 shows an exemplary LITT lateral ablation core prepared by the second process according to some embodiments of the present specification.
如图8所示，LITT侧向消融探针800包括探针主体810，连接面820，以及透镜830。连接面820为主体810与透镜830之间的连接界面。As shown in FIG. 8 , the LITT lateral ablation probe 800 includes a probe body 810 , a connection surface 820 , and a lens 830 . The connection surface 820 is the connection interface between the main body 810 and the lens 830 .
探针主体810呈圆柱体状。探针主体810由针芯和位于针芯外周的硬质包层构成。所述针芯由纯二氧化硅材料制成。所述硬质包层由技术增强型包层二氧化硅(TECS)材料制成。The probe body 810 is cylindrical. The probe body 810 is composed of a needle core and a hard cladding located on the outer periphery of the needle core. The needle core is made of pure silicon dioxide material. The hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
所述针芯的直径(外径)为，例如，550-650μm。在一些实施例中，针芯的直径(外径)为560μm。在一些实施例中，针芯的直径(外径)为570μm。在一些实施例中，针芯的直径(外径)为580μm。在一些实施例中，针芯的直径(外径)为590μm。在一些实施例中，针芯的直径(外径)为600μm。在一些实施例中，针芯的直径(外径)为610μm。在一些实施例中，针芯的直径(外径)为620μm。在一些实施例中，针芯的直径(外径)为630μm。在一些实施例中，针芯的直径(外径)为640μm。The diameter (outer diameter) of the needle core is, for example, 550-650 μm. In some embodiments, the diameter (outer diameter) of the needle core is 560 μm. In some embodiments, the diameter (outer diameter) of the needle core is 570 μm. In some embodiments, the diameter (outer diameter) of the needle core is 580 μm. In some embodiments, the diameter (outer diameter) of the needle core is 590 μm. In some embodiments, the diameter (outer diameter) of the needle core is 600 μm. In some embodiments, the diameter (outer diameter) of the needle core is 610 μm. In some embodiments, the diameter (outer diameter) of the needle core is 620 μm. In some embodiments, the diameter (outer diameter) of the needle core is 630 μm. In some embodiments, the diameter (outer diameter) of the needle core is 640 μm.
所述硬质包层的厚度为，例如，5-30μm。在一些实施例中，所述硬质包层的厚度为5μm。在一些实施例中，所述硬质包层的厚度为10μm。在一些实施例中，所述硬质包层的厚度为15μm。在一些实施例中，所述硬质包层的厚度为20μm。在一些实施例中，所述硬质包层的厚度为25μm。在一些实施例中，所述硬质包层的厚度为30μm。The thickness of the hard cladding is, for example, 5-30 μm. In some embodiments, the hard cladding layer has a thickness of 5 μm. In some embodiments, the hard cladding layer has a thickness of 10 μm. In some embodiments, the hard cladding has a thickness of 15 μm. In some embodiments, the hard cladding has a thickness of 20 μm. In some embodiments, the hard cladding has a thickness of 25 μm. In some embodiments, the hard cladding has a thickness of 30 μm.
连接面820采用特定精度(例如，0.1μm，0.5μm，1μm，2μm，3μm等)的金刚石膜，去除一定数值孔径(例如，0.35NA，0.36NA，0.37NA，0.38NA，0.39NA，0.4NA，0.41NA，0.42NA，0.43NA，0.44NA，0.45NA等)的特殊阶跃折射率多模材质纤芯，并在外围设置技术增强型包层二氧化硅(TECS)硬质包层作为主料。进而通过将特定成分的悬浮液，涂覆于二氧化硅胶体基膜表面，而形成垂直于探针主体810端部(平端)的光洁面。The connection surface 820 uses a diamond film with specific precision (for example, 0.1 μm, 0.5 μm, 1 μm, 2 μm, 3 μm, etc.), and removes a certain numerical aperture (for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA) , 0.41NA, 0.42NA, 0.43NA, 0.44NA, 0.45NA, etc.) special step refractive index multi-mode material core, and a technology-enhanced cladding silica (TECS) hard cladding is set on the periphery as the main material. Then, a suspension of specific components is coated on the surface of the silica colloidal base film to form a smooth surface perpendicular to the end (flat end) of the probe body 810 .
示例性地，所述悬浮液包含合成无定形二氧化硅、H 2O以及丙烷-1,2-二醇。在一些实施例中，按质量分数，所述悬浮液包含10％-20％的合成无定形二氧化硅、20％-30％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、20％-30％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含30％-40％的合成无定形二氧化硅、20％-30％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、10％-20％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、30％-40％的H 2O、45％-55％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、20％-30％的H 2O、35％-45％的(丙烷-1,2-二醇)。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、20％-30％的H 2O、55％-65％的(丙烷-1,2-二醇)。 Illustratively, the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol. In some embodiments, by mass fraction, the suspension contains 10%-20% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 30%-40% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 10%-20% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 30%-40% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 35%-45% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 55%-65% (propane-1,2 -diol).
在一些实施例中，透镜830采用蓝宝石透镜。如图所示，透镜830包括直角(90°)、底角和顶角。其中，顶角的角度可以根据底角的角度确定。该直角、底角和顶角满足一定关系，如顶角的角度等于90°减去给定的底角的角度。需要说明的是，在本实施例中，主体810及透镜830均为圆柱体，透镜830为斜切的圆柱体。此处的直角、底角和顶角为从平行于斜切面视角下形成的二维图像中透镜830各边形成的角度。In some embodiments, lens 830 utilizes a sapphire lens. As shown, lens 830 includes a right angle (90°), a base angle, and an apex angle. Among them, the angle of the top corner can be determined based on the angle of the bottom corner. The right angle, base angle and vertex angle satisfy a certain relationship, for example, the angle of the vertex angle is equal to 90° minus the given angle of the base angle. It should be noted that in this embodiment, the main body 810 and the lens 830 are both cylinders, and the lens 830 is a beveled cylinder. The right angle, base angle and vertex angle here are the angles formed by each side of the lens 830 in a two-dimensional image formed from a viewing angle parallel to the oblique plane.
所述底角在一定角度范围内。在一些实施例中，底角为50°-45°。相应地，顶角为40°-45°。在一些实施例中，底角为52°-47°。相应地，顶角为38°-43°。在一些实施例中，底角为54°-49°。相应地，顶角为36°-41°。在一些实施例中，底角为56°-51°。相应地，顶角为34°-39°。The base angle is within a certain angle range. In some embodiments, the base angle is 50°-45°. Correspondingly, the vertex angle is 40°-45°. In some embodiments, the base angle is 52°-47°. Correspondingly, the vertex angle is 38°-43°. In some embodiments, the base angle is 54°-49°. Correspondingly, the vertex angle is 36°-41°. In some embodiments, the base angle is 56°-51°. Correspondingly, the vertex angle is 34°-39°.
透镜830的底角和直角之间的直角边(即形成所述底角的直角边)的长度，即圆柱形透镜的直径，等于探针主体810的外径，即技术增强型包层二氧化硅(TECS)硬质包层的外径。The length of the right-angled side between the base angle and the right angle of the lens 830 (i.e., the right-angled side forming the base angle), that is, the diameter of the cylindrical lens, is equal to the outer diameter of the probe body 810, which is the technology-enhanced cladding dioxide The outer diameter of the silicon (TECS) hard cladding.
连接面820与透镜830的底角和直角之间的直角边所在的面，通过电弧焊接或钨(如钨丝)、铱(如铱丝)等材料的高温熔融而熔接，并在钨或铱的高温熔融熔接选择下行钨丝或铱丝下火抛光工艺，即对熔接面进行火抛光，最终形成LITT侧向消融探针800。火抛光，又称火焰抛光，可以采用火焰抛光机完成。该工艺结合透镜以及与水平面呈特定角度范围内(例如，40°-45°，38°-43°，36°-41°，34°-39°)的透镜顶角角度，提升了LITT侧向消融探针800的性能。The surface where the right-angled side between the bottom angle and the right angle of the connecting surface 820 and the lens 830 is welded by arc welding or high-temperature melting of tungsten (such as tungsten wire), iridium (such as iridium wire) and other materials, and the tungsten or iridium For high-temperature fusion welding, the downlink tungsten wire or iridium wire fire polishing process is selected, that is, the welding surface is fire polished, and finally the LITT lateral ablation probe 800 is formed. Fire polishing, also known as flame polishing, can be done using a flame polishing machine. This process combines the lens and the lens vertex angle within a specific angle range from the horizontal plane (for example, 40°-45°, 38°-43°, 36°-41°, 34°-39°) to improve the LITT lateral Ablation Probe 800 performance.
在该工艺下，LITT侧向消融探针800，以发射角为78°左右的射束，均匀发射受控激光到目标对象，以实现病灶组织消融。Under this process, the LITT lateral ablation probe 800 uses a beam with an emission angle of about 78° to uniformly emit controlled laser light to the target object to achieve ablation of the lesion tissue.
在一些实施例中，透镜830也可以是斜切的半球形透镜(如蓝宝石半球透镜)。斜切的半球透镜的直径为，例如，0.5mm，0.6mm，0.7mm，0.8mm，0.9mm，1mm等。在一些实施例中，透镜830还可以是斜切的半椭球形透镜(如蓝宝石半椭球透镜)。斜切的半椭球透镜的长半轴为，例如，0.5mm，0.6mm，0.7mm，0.8mm，0.9mm，1mm，1.1mm，1.2mm等。斜切的半椭球透镜的扁率为，例如，1/298，1/250，1/200，1/150，1/100，1/50等。In some embodiments, the lens 830 may also be a beveled hemispherical lens (such as a sapphire hemispherical lens). The diameter of the beveled hemispherical lens is, for example, 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1 mm, etc. In some embodiments, the lens 830 may also be a beveled semi-ellipsoidal lens (such as a sapphire semi-ellipsoidal lens). The long semi-axis of the beveled semi-ellipsoidal lens is, for example, 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1 mm, 1.1 mm, 1.2 mm, etc. The flattening of the beveled semi-ellipsoidal lens is, for example, 1/298, 1/250, 1/200, 1/150, 1/100, 1/50, etc.
相应地，LITT侧向消融探针800的制备工艺(即第二种工艺)包括如下步骤：Accordingly, the preparation process of the LITT lateral ablation probe 800 (i.e., the second process) includes the following steps:
步骤S8-1：对主体810的端面光洁化。Step S8-1: Smooth the end surface of the main body 810.
此处主体810的端面是指主体810与透镜830之间的连接界面，即连接面820。主体810的端面与主体810的轴线垂直。采用特定精度的金刚石膜，去除一定数值孔径的特殊阶跃折射率多模材质纤芯，并在外围设置技术增强型包层二氧化硅(TECS)硬质包层作为主料。进而通过将特定成分的悬浮液，涂覆于二氧化硅胶体基膜表面，使探针主体810的端部形成光洁面。示例性地，所述悬浮液包含合成无定形二氧化硅、H 2O以及丙烷-1,2-二醇。在一些实施例中，按质量分数，所述悬浮液包含20％-30％的合成无定形二氧化硅、20％-30％的H 2O、45％-55％的(丙烷-1,2-二醇)。 Here, the end surface of the main body 810 refers to the connection interface between the main body 810 and the lens 830, that is, the connection surface 820. The end surface of the main body 810 is perpendicular to the axis of the main body 810 . A specific precision diamond film is used to remove the core of a special step refractive index multi-mode material with a certain numerical aperture, and a technology-enhanced cladding silica (TECS) hard cladding is set as the main material on the periphery. Furthermore, a suspension of specific components is coated on the surface of the silica colloidal base film to form a smooth surface at the end of the probe body 810 . Illustratively, the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol. In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
步骤S8-2：将主体810和透镜830进行熔接，形成LITT侧向消融探针800。Step S8-2: Weld the main body 810 and the lens 830 to form the LITT lateral ablation probe 800.
将主体810和透镜830通过特定的高温处理手段进行熔接，使透镜830与主体810建立稳定的连接。在一些实施例中，可以通过电弧焊接对主体810和透镜830进行熔接。在另一些实施例中，也可以采用钨(如钨丝)、铱(如铱丝)等材料的高温熔融，对主体810和透镜830进行熔接。在钨或铱的高温熔融熔接选择下行钨丝或铱丝下火抛光工艺，即对熔接面进行火抛光，最终形成LITT侧向消融探针800。The main body 810 and the lens 830 are welded using a specific high-temperature treatment method to establish a stable connection between the lens 830 and the main body 810 . In some embodiments, body 810 and lens 830 may be welded by arc welding. In other embodiments, high-temperature melting of materials such as tungsten (such as tungsten wire) and iridium (such as iridium wire) can also be used to weld the main body 810 and the lens 830 . During the high-temperature melting and welding of tungsten or iridium, a tungsten wire or iridium wire fire polishing process is selected, that is, the welding surface is fire polished, and finally the LITT lateral ablation probe 800 is formed.
图9所示为根据本说明书一些实施例的示例性LITT周向消融探针。Figure 9 illustrates an exemplary LITT circumferential ablation probe in accordance with some embodiments of the present specification.
如图9所示，LITT周向消融探针900包括探针主体910。As shown in FIG. 9 , LITT circumferential ablation probe 900 includes probe body 910 .
探针主体910由针芯和位于针芯外周的硬质包层构成。所述针芯由纯二氧化硅材料制成。所述硬质包层由技术增强型包层二氧化硅(TECS)材料制成。The probe body 910 is composed of a needle core and a hard cladding located on the outer periphery of the needle core. The needle core is made of pure silicon dioxide material. The hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
所述针芯的直径(外径)为，例如，550-650μm。在一些实施例中，针芯的直径(外径)为560μm。在一些实施例中，针芯的直径(外径)为570μm。在一些实施例中，针芯的直径(外径)为580μm。在一些实施例中，针芯的直径(外径)为590μm。在一些实施例中，针芯的直径(外径)为600μm。在一些实施例中，针芯的直径(外径)为610μm。在一些实施例中，针芯的直径(外径)为620μm。在一些实施例中，针芯的直径(外径)为630μm。在一些实施例中，针芯的直径(外径)为640μm。The diameter (outer diameter) of the needle core is, for example, 550-650 μm. In some embodiments, the diameter (outer diameter) of the needle core is 560 μm. In some embodiments, the diameter (outer diameter) of the needle core is 570 μm. In some embodiments, the diameter (outer diameter) of the needle core is 580 μm. In some embodiments, the diameter (outer diameter) of the needle core is 590 μm. In some embodiments, the diameter (outer diameter) of the needle core is 600 μm. In some embodiments, the diameter (outer diameter) of the needle core is 610 μm. In some embodiments, the diameter (outer diameter) of the needle core is 620 μm. In some embodiments, the diameter (outer diameter) of the needle core is 630 μm. In some embodiments, the diameter (outer diameter) of the needle core is 640 μm.
所述硬质包层的厚度为，例如，5-30μm。在一些实施例中，所述硬质包层的厚度为5μm。在一些实施例中，所述硬质包层的厚度为10μm。在一些实施例中，所述硬质包层的厚度为15μm。在一些实施例中，所述硬质包层的厚度为20μm。在一些实施例中，所述硬质包层的厚度为25μm。在一些实施例中，所述硬质包层的厚度为30μm。The thickness of the hard cladding is, for example, 5-30 μm. In some embodiments, the hard cladding layer has a thickness of 5 μm. In some embodiments, the hard cladding layer has a thickness of 10 μm. In some embodiments, the hard cladding has a thickness of 15 μm. In some embodiments, the hard cladding has a thickness of 20 μm. In some embodiments, the hard cladding has a thickness of 25 μm. In some embodiments, the hard cladding has a thickness of 30 μm.
在本实施例中，探针主体910的远端(靠近目标对象的端部)，设置锥形面920。所述锥形面的直径由初始直径逐渐缩小至预设直径。所述初始直径即为上述针芯直径与包层厚度之和。示例性地，所述初始直径为630μm。所述预设直径即为探针主体910的远端端部的直径。所述预设直径为50-150μm。在一些实施例中，所述预设直径为60μm。在一些实施例中，所述预设直径为70μm。在一些实施例中，所述预设直径为80μm。在一些实施例中，所述预设直径为90μm。在一些实施例中，所述预设直径为100μm。在一些实施例中，所述预设直径为110μm。在一些实施例中，所述预设直径为120μm。在一些实施例中，所述预设直径为130μm。在一些实施例中，所述预设直径为140μm。In this embodiment, a tapered surface 920 is provided at the distal end of the probe body 910 (the end close to the target object). The diameter of the tapered surface gradually decreases from the initial diameter to the preset diameter. The initial diameter is the sum of the diameter of the needle core and the thickness of the cladding. Exemplarily, the initial diameter is 630 μm. The preset diameter is the diameter of the distal end of the probe body 910 . The preset diameter is 50-150 μm. In some embodiments, the preset diameter is 60 μm. In some embodiments, the preset diameter is 70 μm. In some embodiments, the preset diameter is 80 μm. In some embodiments, the preset diameter is 90 μm. In some embodiments, the preset diameter is 100 μm. In some embodiments, the preset diameter is 110 μm. In some embodiments, the preset diameter is 120 μm. In some embodiments, the preset diameter is 130 μm. In some embodiments, the preset diameter is 140 μm.
在锥形面920上设置有凹槽。传导至LITT周向消融探针900的激光可以从所述凹槽中出射，以治疗目标对象，实现病灶组织的消融。所述凹槽呈一定花纹状(例如，螺纹状)沿锥形面920均匀(弥散)分布，并且互相不重叠。LITT周向消融探针，又称为LITT周向弥散消融探针。所述凹槽具有一定深度。示例性地，所述凹槽的深度为5-35μm。在一些实施例中，所述凹槽的深度为10μm。在一些实施例中，所述凹槽的深度为15μm。在一些实施例中，所述凹槽的深度为20μm。在一些实施例中，所述凹槽的深度为25μm。在一些实施例中，所述凹槽的深度为30μm。Grooves are provided on the tapered surface 920 . The laser light directed to the LITT circumferential ablation probe 900 can be emitted from the groove to treat the target object and achieve ablation of the lesion tissue. The grooves are evenly (dispersed) distributed along the tapered surface 920 in a certain pattern shape (for example, thread shape) and do not overlap with each other. LITT circumferential ablation probe, also known as LITT circumferential diffusion ablation probe. The groove has a certain depth. Exemplarily, the depth of the groove is 5-35 μm. In some embodiments, the groove has a depth of 10 μm. In some embodiments, the groove has a depth of 15 μm. In some embodiments, the groove has a depth of 20 μm. In some embodiments, the groove has a depth of 25 μm. In some embodiments, the groove has a depth of 30 μm.
在一些实施例中，所述凹槽的分布花纹为单螺纹形状(螺旋状)、多螺纹交叉形状(例如，双螺纹交叉，如图9中所示)、菱形网格形状、蜂窝形状等，或其组合。需要注意的是，上述列举的单螺纹形状、多螺纹交叉形状、菱形网格形状、蜂窝形状仅为具体示例，并不限定凹槽的具体分布花纹，其还可以是其他任意合理的花纹，仅需满足凹槽的具体分布形状沿锥形面920均匀(弥散)分布，且不重叠即可。In some embodiments, the distribution pattern of the grooves is a single thread shape (spiral shape), a multi-thread cross shape (for example, a double thread cross, as shown in Figure 9), a rhombus grid shape, a honeycomb shape, etc., or combination thereof. It should be noted that the single thread shape, multi-thread cross shape, rhombus grid shape, and honeycomb shape listed above are only specific examples and do not limit the specific distribution pattern of the grooves. It can also be any other reasonable pattern. It is required that the specific distribution shape of the grooves is evenly (dispersed) distributed along the tapered surface 920 and does not overlap.
在一些实施例中，锥形面920及其上设置的呈一定花纹状均匀分布的凹槽可以通过光电设备(例如，光机)雕刻形成。示例性地，锥形面920以及其上设置的呈交叉螺纹状分布的凹槽分别可以通过图10和11所描述的光电设备和方法雕刻形成。在一些实施例中，锥形面920及其上设置的凹槽也可以通过其他方式加工而成，例如，机械加工。In some embodiments, the tapered surface 920 and the evenly distributed grooves arranged in a certain pattern on the tapered surface 920 can be formed by engraving with an optoelectronic device (for example, an optical machine). For example, the tapered surface 920 and the cross-threaded grooves provided thereon can be carved and formed by the optoelectronic equipment and method described in FIGS. 10 and 11 , respectively. In some embodiments, the tapered surface 920 and the groove provided thereon can also be processed by other methods, such as mechanical processing.
图10是根据本说明书一些实施例所示的示例性锥形面加工示意图。Figure 10 is a schematic diagram of an exemplary tapered surface processing according to some embodiments of the present specification.
在本实施例中，锥形面920是通过雕锥设备1000雕刻形成。雕锥设备1000包括终端1001，激光器控制器1002，激光器1003，反射镜1004-1和1004-2，快门1005，快门控制器1006，激光功率衰减器1007，衍射分束透镜单元1008，聚焦透镜单元1009，滑轨1010，固定器件1011，运动驱动器1012，和运动驱动控制器1013。In this embodiment, the tapered surface 920 is carved and formed by the tapered engraving device 1000 . The cone engraving equipment 1000 includes a terminal 1001, a laser controller 1002, a laser 1003, reflectors 1004-1 and 1004-2, a shutter 1005, a shutter controller 1006, a laser power attenuator 1007, a diffraction beam splitting lens unit 1008, and a focusing lens unit. 1009, slide rail 1010, fixing device 1011, motion driver 1012, and motion drive controller 1013.
其中，终端1001连接并控制激光器控制器1002、快门控制器1006和运动驱动控制器1013。激光器控制器1002连接并控制激光器1003发射激光。终端1101可以为，例如，计算机。激光器1003可以是高功率CO 2连续波激光器。反射镜1004-1和1004-2可以采用银镜。快门1005可以为电动快门。快门控制器1006连接并控制快门1005的开关，以控制激光光路的开闭。衍射分束透镜单元1008和聚焦透镜单元1009用于对激光光束进行分束，形成两束激光，并分别聚焦。聚焦透镜单元1009可以为，例如，锌化硒透镜。运动驱动控制器1013连接并控制运动驱动器1012，以驱动待雕锥工件1015运动，例如，平移和/或旋转。 Among them, the terminal 1001 connects to and controls the laser controller 1002, the shutter controller 1006 and the motion drive controller 1013. The laser controller 1002 connects and controls the laser 1003 to emit laser light. The terminal 1101 may be, for example, a computer. Laser 1003 may be a high power CO2 continuous wave laser. Reflectors 1004-1 and 1004-2 can use silver mirrors. Shutter 1005 may be an electric shutter. The shutter controller 1006 is connected to and controls the switch of the shutter 1005 to control the opening and closing of the laser light path. The diffraction beam splitting lens unit 1008 and the focusing lens unit 1009 are used to split the laser beam to form two laser beams and focus them respectively. The focusing lens unit 1009 may be, for example, a zinc selenide lens. The motion drive controller 1013 is connected to and controls the motion driver 1012 to drive the workpiece 1015 to be tapered to move, for example, translation and/or rotation.
通过雕锥设备1000雕刻锥形面920的过程包括如下步骤：The process of carving the cone surface 920 by the cone carving device 1000 includes the following steps:
步骤S10-1：将待雕锥工件1015的两端分别固定于滑轨1010和固定器件1011。固定器件1011连接于运动驱动器1012。固定器件1011可以是夹具。所述夹具可以夹持固定待雕锥工件1015的一端。Step S10-1: Fix both ends of the workpiece 1015 to be carved to the slide rail 1010 and the fixing device 1011 respectively. The fixing device 1011 is connected to the motion driver 1012 . Fixing device 1011 may be a clamp. The clamp can clamp and fix one end of the workpiece 1015 to be tapered.
步骤S10-2：通过终端1001使激光器控制器1002控制激光器1003发射激光。Step S10-2: Use the terminal 1001 to cause the laser controller 1002 to control the laser 1003 to emit laser.
激光器1003产生的激光具有特定功率和波长。产生的激光的功率为，例如，20-40W的范围内。在一些实施例中，产生的激光的功率为25W。在一些实施例中，产生的激光的功率为30W。在一些实施例中，产生的激光的功率为35W。产生的激光的波长约为10600nm。激光经由反射镜1004-1反射至快门1005。 Laser 1003 generates laser light with a specific power and wavelength. The power of the generated laser is, for example, in the range of 20-40W. In some embodiments, the power of the laser generated is 25W. In some embodiments, the power of the laser generated is 30W. In some embodiments, the power of the laser generated is 35W. The wavelength of the laser produced is approximately 10600nm. The laser light is reflected to the shutter 1005 via the mirror 1004-1.
步骤S10-3：通过终端1001使快门控制器1006控制快门1005打开，激光发射至激光功率衰减器1007进行功率衰减处理。Step S10-3: The shutter controller 1006 controls the shutter 1005 to open through the terminal 1001, and the laser is emitted to the laser power attenuator 1007 for power attenuation processing.
激光功率衰减器1007使输入的激光功率进行衰减一定比例，例如，10％，20％，30％，40％，50％，60％，70％，80％，90％等，即进行功率衰减处理。激光功率衰减器1007输出的激光功率(即衰减处理后的激光功率)在一定的范围内，例如，3-20W。在一些实施例中，衰减处理后的激光功率为6-15W。在一些实施例中，衰减处理后的激光功率为6.6-11.2W。激光经过上述衰减处理后，传输至反射镜1004-2反射，并传递至衍射分束透镜单元1008。衍射分束透镜单元1008可以是针对所述激光波长定制的分束透镜。The laser power attenuator 1007 attenuates the input laser power by a certain proportion, for example, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80%, 90%, etc., that is, performs power attenuation processing. . The laser power output by the laser power attenuator 1007 (that is, the laser power after attenuation processing) is within a certain range, for example, 3-20W. In some embodiments, the laser power after attenuation treatment is 6-15W. In some embodiments, the laser power after attenuation treatment is 6.6-11.2W. After the laser undergoes the above attenuation processing, it is transmitted to the reflector 1004-2 for reflection, and then transmitted to the diffraction beam splitting lens unit 1008. The diffraction beam splitting lens unit 1008 may be a beam splitting lens customized for the laser wavelength.
步骤S10-4：功率衰减处理后的激光光束经衍射分束透镜单元1008分为两束激光，该两束激光经过聚焦透镜单元1009聚焦至待雕锥工件1015表面。Step S10 - 4 : The laser beam after power attenuation processing is split into two laser beams by the diffraction beam splitting lens unit 1008 , and the two laser beams are focused onto the surface of the workpiece 1015 to be coned by the focusing lens unit 1009 .
待雕锥工件1015包括纤芯和纤芯外围的硬质包层。所述纤芯由纯二氧化硅材料制成。所述纤芯外围的硬质包层由技术增强型包层二氧化硅(TECS)材料制成。两束激光分别在待雕锥工件1015表面形成光斑1014-1和1014-2。光斑1014-1和1014-2聚焦至待雕锥工件1015的外围硬质包层上。The workpiece 1015 to be tapered includes a fiber core and a hard cladding around the core. The core is made of pure silica material. The hard cladding around the core is made of Technology Enhanced Cladding Silica (TECS) material. The two laser beams respectively form light spots 1014-1 and 1014-2 on the surface of the workpiece 1015 to be carved. The light spots 1014-1 and 1014-2 are focused on the peripheral hard cladding of the workpiece 1015 to be carved.
步骤S10-5：通过终端1001使运动驱动控制器1013控制运动驱动器1012，以驱动待雕锥工件1015运动。Step S10-5: Use the terminal 1001 to cause the motion drive controller 1013 to control the motion driver 1012 to drive the movement of the workpiece 1015 to be tapered.
在待雕锥工件1015运动(平移、旋转等)过程中，激光形成的光斑1014-1和1014-2在待雕锥工件1015表面进行雕刻，最终形成锥形面920。During the movement (translation, rotation, etc.) of the workpiece 1015 to be carved with a cone, the light spots 1014-1 and 1014-2 formed by the laser are engraved on the surface of the workpiece 1015 to be carved with a cone, and finally a conical surface 920 is formed.
需要注意的是，本说明书上述各步骤执行的顺序不作具体限定，同时，部分步骤也可以合并执行。It should be noted that the order in which the above-mentioned steps are performed in this specification is not specifically limited, and at the same time, some steps can also be performed in combination.
图11是根据本说明书一些实施例所示的示例性交叉螺纹状分布的凹槽的加工示意图。11 is a schematic diagram of processing of exemplary cross-threaded grooves according to some embodiments of the present specification.
在本实施例中，交叉螺纹状分布的凹槽是通过雕花设备1100在待雕花工件1110表面雕刻形成。所述待雕花工件1110为经过上述步骤S10-1至S10-5处理的，具有锥形面920的工件。雕花设备1100包括终端1101，激光器控制器1102，激光器1103，反射镜1104，透镜组1005，滑轨1106，固定器件1107，运动驱动器1108，和运动驱动控制器1109。In this embodiment, cross-threaded grooves are carved and formed on the surface of the workpiece 1110 to be carved by the engraving device 1100 . The workpiece 1110 to be carved is a workpiece with a tapered surface 920 that has been processed through the above steps S10-1 to S10-5. The engraving equipment 1100 includes a terminal 1101, a laser controller 1102, a laser 1103, a reflector 1104, a lens group 1005, a slide rail 1106, a fixing device 1107, a motion driver 1108, and a motion drive controller 1109.
其中，终端1101连接并控制激光器控制器1102和运动驱动控制器1109。终端1101可以为，例如，计算机。激光器控制器1102连接并控制激光器1103发射激光。激光器1103可以是高功率CO 2连续波激光器。反射镜1104可以采用银镜。透镜组1005可以包括一个或多个透镜。所述一个或多个透镜包括凹透镜和/或凸透镜。运动驱动控制器1109连接并控制运动驱动器1108，以驱动待雕花工件1110运动，例如，平移和/或旋转。 Among them, the terminal 1101 connects and controls the laser controller 1102 and the motion drive controller 1109. The terminal 1101 may be, for example, a computer. The laser controller 1102 connects and controls the laser 1103 to emit laser light. Laser 1103 may be a high power CO2 continuous wave laser. The reflector 1104 may be a silver mirror. Lens group 1005 may include one or more lenses. The one or more lenses include concave lenses and/or convex lenses. The motion drive controller 1109 is connected to and controls the motion driver 1108 to drive the workpiece 1110 to be carved to move, for example, translation and/or rotation.
通过雕花设备1100雕刻交叉螺纹状分布的凹槽的过程包括如下步骤：The process of engraving cross-threaded grooves by the engraving device 1100 includes the following steps:
步骤S11-1：将待雕花工件1110的两端分别固定于滑轨1106和固定器件1107。固定器件1107连接于运动驱动器1108。固定器件1107可以是夹具。所述夹具可以夹持固定待雕花工件1110的一端。Step S11-1: Fix both ends of the workpiece 1110 to be carved to the slide rail 1106 and the fixing device 1107 respectively. The fixation device 1107 is connected to the motion driver 1108 . Fixing device 1107 may be a clamp. The clamp can clamp and fix one end of the workpiece 1110 to be carved.
步骤S11-2：通过终端1101使激光器控制器1102控制激光器1103发射激光。Step S11 - 2 : The terminal 1101 enables the laser controller 1102 to control the laser 1103 to emit laser light.
激光器1103产生的激光具有特定功率和波长。产生的激光的功率为，例如，20-40W的范围内。在一些实施例中，产生的激光的功率为25W。在一些实施例中，产生的激光的功率为30W。在一些实施例中，产生的激光的功率为35W。产生的激光的波长约为10600nm。在本实施例中，激光器1103可以是高功率CO 2连续波激光器。对于高功率CO 2连续波激光器发出的连续波，待雕花工件1110的损伤阈值约为250kW/cm 2；对于高功率CO 2连续波激光器的脉冲波(例如，10ns的脉冲波)，待雕花工件1110的损伤阈值约为1GW/cm 2。 The laser generated by the laser 1103 has a specific power and wavelength. The power of the generated laser is, for example, in the range of 20-40W. In some embodiments, the power of the generated laser is 25W. In some embodiments, the power of the generated laser is 30W. In some embodiments, the power of the generated laser is 35W. The wavelength of the generated laser is about 10600nm. In this embodiment, the laser 1103 can be a high-power CO2 continuous wave laser. For the continuous wave emitted by the high-power CO2 continuous wave laser, the damage threshold of the workpiece 1110 to be engraved is about 250kW/ cm2 ; for the pulse wave of the high-power CO2 continuous wave laser (for example, a pulse wave of 10ns), the damage threshold of the workpiece 1110 to be engraved is about 1GW/ cm2 .
步骤S11-3：激光经透镜组1105，聚焦至待雕花工件1110表面。Step S11-3: The laser is focused on the surface of the workpiece 1110 to be carved through the lens group 1105.
激光经透镜组1105，在待雕花工件1110的锥形面上形式特定能量和尺寸的光斑。例如，光斑的直径为30-60μm。在一些实施例中，光斑的直径为35μm。在一些实施例中，光斑的直径为40μm。在一些实施例中，光斑的直径为45μm。在一些实施例中，光斑的直径为50μm。在一些实施例中，光斑的直径为55μm。光斑的能量高于待雕花工件1110表面材料消融的辐照度。待雕花工件1110表面材料的辐照度接近玻璃消融的辐照度为3.1×10 5W/cm 2。 The laser passes through the lens group 1105 and forms a light spot of specific energy and size on the conical surface of the workpiece 1110 to be carved. For example, the diameter of the light spot is 30-60 μm. In some embodiments, the spot diameter is 35 μm. In some embodiments, the diameter of the light spot is 40 μm. In some embodiments, the spot diameter is 45 μm. In some embodiments, the diameter of the light spot is 50 μm. In some embodiments, the spot diameter is 55 μm. The energy of the light spot is higher than the irradiance of the surface material ablation of the workpiece 1110 to be carved. The irradiance of the surface material of the workpiece 1110 to be carved is close to the irradiance of glass ablation, which is 3.1×10 5 W/cm 2 .
在一些实施例中，透镜组1105可以包括顺序排列的第一凹透镜、第一凸透镜和第二凹透镜。第一凹透镜和第一凸透镜用于将激光束的直径扩展到第一直径，第二凹透镜用于将第一直径的激光束聚焦至待雕花工件1110表面，形成上述光斑。In some embodiments, the lens group 1105 may include a first concave lens, a first convex lens, and a second concave lens arranged in sequence. The first concave lens and the first convex lens are used to expand the diameter of the laser beam to the first diameter, and the second concave lens is used to focus the laser beam of the first diameter onto the surface of the workpiece 1110 to be engraved to form the above-mentioned light spot.
步骤S11-4：通过终端1101使运动驱动控制器1109控制运动驱动器1108，以驱动待雕花工件1110运动。Step S11-4: Use the terminal 1101 to cause the motion drive controller 1109 to control the motion driver 1108 to drive the workpiece 1110 to be engraved to move.
在待雕花工件1110运动(平移、旋转等)过程中，激光形成的光斑在待雕花工件1110表面进行雕刻，最终在待雕花工件1110的锥形面上形成交叉螺纹状分布的凹槽。During the movement (translation, rotation, etc.) of the workpiece 1110 to be carved, the light spot formed by the laser engraves on the surface of the workpiece 1110 to be carved, and finally forms grooves distributed in a cross-thread shape on the conical surface of the workpiece 1110 to be carved.
在一些实施例中，在使用雕花设备1100雕刻交叉螺纹状分布的凹槽的过程，可以使用空气冷却系统，吹扫雕刻的凹槽，清除凹槽内部和周围的颗粒物(如灰尘、杂质)、熔融物等，保持加工区域的表面洁净。In some embodiments, during the process of using the engraving device 1100 to carve cross-threaded grooves, an air cooling system can be used to blow the engraved grooves and remove particles (such as dust, impurities) in and around the grooves. Molten materials, etc., keep the surface of the processing area clean.
需要注意的是，本说明书上述各步骤执行的顺序不作具体限定，同时，部分步骤也可以合并执行。It should be noted that the order in which the above-mentioned steps are performed in this specification is not specifically limited, and at the same time, some steps can also be performed in combination.
通过图10和11所述的光电设备和方法雕刻形成的LITT周向消融探针900，由于凹槽呈一定花纹状(例如，交叉螺纹)沿锥形面920均匀(弥散)分布，因此LITT周向消融探针900的矢量光能分布更加均匀，结合上述测温元件的测温机制，使得周围组织的消融更加均匀且彻底。同时，结合基于LITT周向消融探针900的组织热特性和热损伤算法，使得术中对健康组织的保护，以及消融病理的消融效果，均得到了显著提升。The LITT circumferential ablation probe 900 engraved by the optoelectronic equipment and method described in Figures 10 and 11 has a certain pattern (for example, cross threads) of grooves evenly (diffuse) distributed along the tapered surface 920, so the LITT circumferential The vector light energy distributed to the ablation probe 900 is more evenly distributed, and combined with the temperature measurement mechanism of the above-mentioned temperature measurement element, the ablation of the surrounding tissue is more uniform and complete. At the same time, combined with the tissue thermal characteristics and thermal damage algorithm based on the LITT circumferential ablation probe 900, the protection of healthy tissue during the operation and the ablation effect of ablation pathology have been significantly improved.
图12是根据本说明书一些实施例所示的测试LITT周向消融探针的矢量光能分布的示意图。Figure 12 is a schematic diagram of vector light energy distribution of a LITT circumferential ablation probe tested according to some embodiments of this specification.
在本实施例中，LITT周向消融探针900的矢量光能分布的均匀性可以通过LITT探针极性测试设备1200测试获得。LITT周向消融探针900的矢量光能分布的均匀性可以通过LITT周向消融探针900在不同高度下的圆周空间光分布的极性强度表征。LITT探针极性测试设备1200包括激光器1201，光纤耦合器1202，LITT周向消融集成探针1203，光阑1204，激光测量传感器1205，终端1206，运动驱动器1207，和运动驱动控制器1208。In this embodiment, the uniformity of the vector light energy distribution of the LITT circumferential ablation probe 900 can be tested by the LITT probe polarity testing device 1200 . The uniformity of the vector light energy distribution of the LITT circumferential ablation probe 900 can be characterized by the polar intensity of the circumferential spatial light distribution of the LITT circumferential ablation probe 900 at different heights. The LITT probe polarity testing device 1200 includes a laser 1201, a fiber coupler 1202, a LITT circumferential ablation integrated probe 1203, an aperture 1204, a laser measurement sensor 1205, a terminal 1206, a motion driver 1207, and a motion drive controller 1208.
其中，激光器1201可以是氦氖激光器。在一些实施例中，所述氦氖激光器为发射激光波长为632.8nm的氦氖激光器。光阑1204用于限制光束的传播。光阑1204安装于激光测量传感器1205前方，以限制激光测量传感器1205接收到的激光，例如，使激光测量传感器1205仅可以接收到特定方向的激光。光阑1204可以是孔径光阑，狭缝光阑等。在一些实施例中，光阑1204可以是狭缝光阑。狭缝光阑的尺寸(即狭缝的宽度)为，例如，0.1-0.5mm。在一些实施例中，狭缝光阑的尺寸为0.2mm。在一些实施例中，狭缝光阑的尺寸为0.3mm。在一些实施例中，狭缝光阑的尺寸为0.4mm。激光测量传感器1205用于接收激光，并生成相应的电信号，以表征接收到的激光的强度。在一些实施例中，激光测量传感器1205可以是圆几何光电二极管激光测量传感器或其他可以测量激光强度的传感器。终端1206连接并控制激光测量传感器1205和运动驱动控制器1208。终端1206可以为，例 如，计算机。光阑1204及激光测量传感器1205固定连接于运动驱动器1207。运动驱动控制器1208连接并控制运动驱动器1207，以驱动光阑1204及激光测量传感器1205运动，例如，平移和/或旋转。The laser 1201 may be a helium-neon laser. In some embodiments, the helium-neon laser is a helium-neon laser emitting a laser wavelength of 632.8 nm. The aperture 1204 is used to limit the propagation of the light beam. The aperture 1204 is installed in front of the laser measurement sensor 1205 to limit the laser received by the laser measurement sensor 1205, for example, so that the laser measurement sensor 1205 can only receive lasers in a specific direction. The aperture 1204 may be an aperture aperture, a slit aperture, etc. In some embodiments, the aperture 1204 may be a slit aperture. The size of the slit aperture (i.e., the width of the slit) is, for example, 0.1-0.5 mm. In some embodiments, the size of the slit aperture is 0.2 mm. In some embodiments, the size of the slit aperture is 0.3 mm. In some embodiments, the size of the slit aperture is 0.4 mm. The laser measurement sensor 1205 is used to receive laser light and generate a corresponding electrical signal to characterize the intensity of the received laser light. In some embodiments, the laser measurement sensor 1205 may be a circular geometry photodiode laser measurement sensor or other sensors that can measure laser intensity. The terminal 1206 is connected to and controls the laser measurement sensor 1205 and the motion drive controller 1208. The terminal 1206 can be, for example, a computer. The aperture 1204 and the laser measurement sensor 1205 are fixedly connected to the motion driver 1207. The motion drive controller 1208 is connected to and controls the motion driver 1207 to drive the aperture 1204 and the laser measurement sensor 1205 to move, for example, translate and/or rotate.
通过LITT探针极性测试设备1200测试LITT周向消融探针900的矢量光能分布的均匀性的过程包括如下步骤：The process of testing the uniformity of the vector light energy distribution of the LITT circumferential ablation probe 900 through the LITT probe polarity testing device 1200 includes the following steps:
步骤S12-1：通过终端1206获取激光测量传感器1205输出的信号，生成特定方位的激光极性强度。Step S12-1: Obtain the signal output by the laser measurement sensor 1205 through the terminal 1206, and generate the laser polarity intensity in a specific direction.
激光器1201生成激光(例如，可见光)，经由空间光路(如光纤)传导至光纤耦合器1202。光纤耦合器1202耦合至LITT周向消融集成探针的LITT探针通道。经由LITT探针通道，激光传输至LITT周向消融探针900并经LITT周向消融探针900上的周向均匀分布凹槽，360度弥散射出矢量光能。该矢量光能经光阑1204限制，入射激光测量传感器1205。激光测量传感器1205接收入射的激光，并生成相应的电信号，以表征接收到的激光的强度。该强度为光阑1204和激光测量传感器1205在该方位下的激光极性强度。The laser 1201 generates laser light (for example, visible light) and conducts it to the optical fiber coupler 1202 via a spatial optical path (such as an optical fiber). Fiber optic coupler 1202 couples to the LITT probe channel of the LITT circumferential ablation integrated probe. Through the LITT probe channel, the laser light is transmitted to the LITT circumferential ablation probe 900 and passes through the circumferentially uniformly distributed grooves on the LITT circumferential ablation probe 900 to emit vector light energy in a 360-degree dispersion. The vector light energy is limited by the aperture 1204 and enters the laser measurement sensor 1205. The laser measurement sensor 1205 receives the incident laser and generates a corresponding electrical signal to represent the intensity of the received laser. This intensity is the laser polarity intensity of the aperture 1204 and the laser measurement sensor 1205 in this orientation.
步骤S12-2：通过终端1206使运动驱动控制器1208控制运动驱动器1207，以驱动光阑1204及激光测量传感器1205沿所述LITT周向消融探针900的锥形面作周向和轴向运动，从而获得激光在整个空间的强度分布(简称空间强度分布)。Step S12-2: The motion drive controller 1208 controls the motion driver 1207 through the terminal 1206 to drive the aperture 1204 and the laser measurement sensor 1205 to move circumferentially and axially along the tapered surface of the LITT circumferential ablation probe 900 , thereby obtaining the intensity distribution of the laser in the entire space (referred to as spatial intensity distribution).
所述整个空间是指沿着LITT周向消融探针900的周向(360度)以及轴向(整体长度)。The entire space refers to the circumference (360 degrees) and axial direction (overall length) of the LITT circumferential ablation probe 900 .
通过运动驱动控制器1208控制运动驱动器1207进行旋转圆周运动，光阑1204及激光测量传感器1205固定连接于运动驱动器1207，因此光阑1204及激光测量传感器1205将围绕LITT周向消融探针900做圆周运动，进而依据上述S12-1步骤中单点极性强度的确定方法，获得LITT周向消融探针900的周向的矢量光分布极性强度。The motion driver 1207 is controlled by the motion drive controller 1208 to perform rotational circular motion. The aperture 1204 and the laser measurement sensor 1205 are fixedly connected to the motion driver 1207. Therefore, the aperture 1204 and the laser measurement sensor 1205 will make a circle around the LITT circumferential ablation probe 900. Movement, and then based on the method for determining the single-point polarity intensity in the above step S12-1, the circumferential vector light distribution polarity intensity of the LITT circumferential ablation probe 900 is obtained.
然后通过运动驱动器1207，调整光阑1204及激光测量传感器1205相对于LITT周向消融探针900长度方向的位置(也可以称为不同高度)，获得不同高度下的LITT周向消融探针900的周向的矢量光分布极性强度，进而得到激光(矢量光)在整个空间的强度分布。Then, the motion driver 1207 is used to adjust the positions of the aperture 1204 and the laser measurement sensor 1205 relative to the length direction of the LITT circumferential ablation probe 900 (which can also be referred to as different heights) to obtain the values of the LITT circumferential ablation probe 900 at different heights. The polar intensity of the circumferential vector light is distributed, thereby obtaining the intensity distribution of the laser (vector light) in the entire space.
利用上述S12-1和S12-2所述方法，对经图10和11所述的光电设备和方法雕刻形成的LITT周向消融探针900进行测试，实验结果证明：LITT周向消融探针900的矢量光能分布非常均匀。因而，LITT周向消融探针900具有更好的性能及治疗效果。The LITT circumferential ablation probe 900 formed by the photoelectric equipment and method described in Figures 10 and 11 was tested using the methods described in S12-1 and S12-2 above. The experimental results proved that: the LITT circumferential ablation probe 900 The vector light energy distribution is very uniform. Therefore, the LITT circumferential ablation probe 900 has better performance and therapeutic effect.
图13是根据本说明书一些实施例所示的利用热电偶测温的示意图。Figure 13 is a schematic diagram of temperature measurement using a thermocouple according to some embodiments of this specification.
如前所述，测温元件(测温元件611或661)，如热电偶1303，可以设置于集成探针(LITT侧向消融集成探针610或LITT周向消融集成探针660)中，以测量LITT探针和/或目标对象的温度。As mentioned above, the temperature measurement element (temperature measurement element 611 or 661), such as the thermocouple 1303, can be disposed in the integrated probe (LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660) to Measure the temperature of the LITT probe and/or target object.
热电偶1303可以连接于供电采集模块1302。供电采集模块1302进一步连接于终端1301。供电采集模块1302对热电偶1303提供电源并将热电偶1303工作过程中采集的温度，传输至终端1301。终端1301可以为，例如，计算机。The thermocouple 1303 may be connected to the power collection module 1302. The power supply collection module 1302 is further connected to the terminal 1301. The power supply acquisition module 1302 provides power to the thermocouple 1303 and transmits the temperature collected during the operation of the thermocouple 1303 to the terminal 1301. Terminal 1301 may be, for example, a computer.
热电偶1303可以是K型热电偶，T型热电偶，E型热电偶等。在本实施例中，热电偶1303为K型热电偶。在一些实施例中，K型热电偶的参数可以为直径40-60μm，阻值46-55欧姆(Ω)，测量精度±0.5-2摄氏度(℃)。示例性地，所述K型热电偶的参数为直径50μm，阻值51Ω，测量精度±1.2℃。The thermocouple 1303 can be a K-type thermocouple, a T-type thermocouple, an E-type thermocouple, etc. In this embodiment, the thermocouple 1303 is a K-type thermocouple. In some embodiments, the parameters of the K-type thermocouple may be a diameter of 40-60 μm, a resistance of 46-55 ohms (Ω), and a measurement accuracy of ±0.5-2 degrees Celsius (°C). For example, the parameters of the K-type thermocouple are 50 μm in diameter, 51 Ω in resistance, and ±1.2°C in measurement accuracy.
在LITT探针工作时，热电偶1303靠近目标对象，同时，LITT探针发出激光消融信号，也会影响到热电偶1303。热电偶1303通过供电采集模块1302连接至终端1301，实时采集并记录目标对象和/或LITT探针温度变化。利用热电偶1303对目标对象和/或LITT探针进行测温，因其贴近组织及探针，因而测温结果较MRTI核磁热成像的远程测温的更为精准。When the LITT probe is working, the thermocouple 1303 is close to the target object. At the same time, the LITT probe emits a laser ablation signal, which will also affect the thermocouple 1303. The thermocouple 1303 is connected to the terminal 1301 through the power supply collection module 1302, and collects and records the temperature changes of the target object and/or LITT probe in real time. Thermocouple 1303 is used to measure the temperature of the target object and/or LITT probe. Because it is close to the tissue and probe, the temperature measurement results are more accurate than the remote temperature measurement of MRTI nuclear magnetic thermal imaging.
图14是根据本说明书一些实施例所示的利用FBG传感器测温的示意图。Figure 14 is a schematic diagram of temperature measurement using an FBG sensor according to some embodiments of this specification.
如前所述，测温元件(测温元件611或661)，如FBG传感器1404-1，可以设置于集成探针(LITT侧向消融集成探针610或LITT周向消融集成探针660)中，以测量LITT探针和/或目标对象的温度。As mentioned above, the temperature measurement element (temperature measurement element 611 or 661), such as the FBG sensor 1404-1, can be disposed in the integrated probe (LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660) , to measure the temperature of the LITT probe and/or target object.
在实际应用于测温时，系统包括终端1401、ASE激光器1402、环形器1403、FBG传感器1404-1、电信光谱分析仪1405、以及温度控制器1406。其中，终端1401可以为，例如，计算机。ASE激光器1402具有超宽带。例 如，ASE激光器1402可以是S、C和L波段三合一，140nm超宽带，1530nm中央波长的ASE激光器。环形器1403可以是超带宽多模高功率环形器。电信光谱分析仪1405为分析范围为600-1700nm的电信光谱分析仪。When actually applied to temperature measurement, the system includes a terminal 1401, an ASE laser 1402, a circulator 1403, an FBG sensor 1404-1, a telecommunications spectrum analyzer 1405, and a temperature controller 1406. The terminal 1401 may be, for example, a computer. The ASE Laser 1402 has ultra wide bandwidth. For example, the ASE laser 1402 may be a three-in-one S, C and L band, 140nm ultra-wideband, 1530nm central wavelength ASE laser. Circulator 1403 may be an ultra-bandwidth multimode high power circulator. Telecommunications spectrum analyzer 1405 is a telecommunications spectrum analyzer with an analysis range of 600-1700nm.
使用特定方式，例如，Multiphysics软件进行数值计算，预测医生在LITT术中期间设定颅内中间质组织温度的空间分布以及热变性程度。用于模拟的几何结构使用了本发明的LITT周向消融探针900(如图中所示)，LITT周向消融探针900远端通过主体910 PEEK或聚碳酸酯PC管套接远端玻璃帽(长度为40-60mm，外径为1.4mm)，设定3cm 3的脑部肿瘤(组织边界)，调谐4W、980nm激光通过LITT周向消融探针900对模拟脑部肿瘤进行120s圆柱消融辐照(如图中四向弥散图示)。 Using specific methods, for example, Multiphysics software performs numerical calculations to predict the spatial distribution of intracranial interstitial tissue temperature and the degree of thermal degeneration set by the physician during LITT. The geometry used for the simulation uses the LITT circumferential ablation probe 900 of the present invention (as shown in the figure). The distal end of the LITT circumferential ablation probe 900 is sleeved with the distal glass through the main body 910 PEEK or polycarbonate PC tube. Cap (length 40-60mm, outer diameter 1.4mm), set a 3cm brain tumor (tissue boundary), tune a 4W, 980nm laser to perform 120s cylindrical ablation of the simulated brain tumor through the LITT circumferential ablation probe 900 Irradiation (as shown in the four-way diffusion diagram in the figure).
通过设定ρ(kg/m 3)是组织密度，c(J/kg·K)是组织比热，K(W/m·K)为组织热导率，T(℃)是组织温度。由于使用了离体模型研发，血流灌注和代谢产热的影响实际上为0；Qi(W/m 3)是激光诱导的热源。此外，初步角度测量证实激光强度以两个方向输送：扩散部分P 1的径向发射功率(W中入射激光功率的89％)和光纤尖端P 2的正向发射功率(W中入射激光功率的11％)，基于这些设定，LITT辐照期间组织的热反应量化为： By setting ρ (kg/m 3 ) as tissue density, c (J/kg·K) as tissue specific heat, K (W/m·K) as tissue thermal conductivity, and T (℃) as tissue temperature. Due to the use of in vitro model development, the effects of blood perfusion and metabolic heat production are actually 0; Qi (W/m 3 ) is the laser-induced heat source. Furthermore, preliminary angular measurements confirmed that the laser intensity is delivered in two directions: the radial emitted power of the diffusion part P1 (89% of the incident laser power in W) and the forward emitted power of the fiber tip P2 (89% of the incident laser power in W). 11%), based on these settings, the thermal response of the tissue during LITT irradiation is quantified as:
Figure PCTCN2022123856-appb-000002
Figure PCTCN2022123856-appb-000002
其中，μ 0(cm -1)是组织的吸收系数，μ s(cm -1)是组织的散射系数，r(m)是与扩散器表面的径向距离，l(m)是扩散器长度。基于扩散器尖端的光束发散角(NA＝0.5)，径向的空间光束强度假定为沿扩散施源器轴的圆柱形，则相应的热源量化为： where μ 0 (cm -1 ) is the absorption coefficient of the tissue, μ s (cm -1 ) is the scattering coefficient of the tissue, r (m) is the radial distance from the diffuser surface, and l (m) is the diffuser length . Based on the beam divergence angle of the diffuser tip (NA=0.5), the radial spatial beam intensity is assumed to be cylindrical along the diffuser axis, and the corresponding heat source quantification is:
Figure PCTCN2022123856-appb-000003
Figure PCTCN2022123856-appb-000003
其中，σ(μm)是激光束的光斑尺寸，z(m)是组织中的轴向深度。where σ (μm) is the spot size of the laser beam and z (m) is the axial depth in the tissue.
假定正向光束分布为高斯分布，热源则换算并量化为：Assuming that the forward beam distribution is Gaussian, the heat source is converted and quantified as:
Figure PCTCN2022123856-appb-000004
Figure PCTCN2022123856-appb-000004
因此应用了980nm或1064nm波长，吸收和散射效应均显著，并引入组织g热特性的散射函数平均余弦。因此，有效衰减系数可代替吸收系数：Therefore, a wavelength of 980 nm or 1064 nm is applied, where both absorption and scattering effects are significant, and the mean cosine of the scattering function of the tissue g-thermal properties is introduced. Therefore, the effective attenuation coefficient can be substituted for the absorption coefficient:
Figure PCTCN2022123856-appb-000005
Figure PCTCN2022123856-appb-000005
将整个组织的初始温度设定为20℃，并对组织外表面进行绝缘处理(即
Figure PCTCN2022123856-appb-000006
其中
Figure PCTCN2022123856-appb-000007
是热流方向)。此外，使用Arrhenius参数(阿伦尼乌斯参数)确定热损伤程度，主要是由于分子反应速率的温度依赖性。作为一级速率过程，使用Arrhenius损伤积分描述组织热损伤(其中Ω是定义不可逆热损伤的无量纲因子，A f(1/s)是频率因子，E x(J/mol)是变性活化能，R是通用气体常数8.314(J/mol·K)，τ(s)是LITT辐照时间。因此，不可逆热变性的开始对应于60℃-65℃的间质组织温度，其中Ω＝1。 The initial temperature of the entire tissue is set to 20°C, and the outer surface of the tissue is insulated (i.e.
Figure PCTCN2022123856-appb-000006
in
Figure PCTCN2022123856-appb-000007
is the direction of heat flow). In addition, the Arrhenius parameter is used to determine the degree of thermal damage, mainly due to the temperature dependence of molecular reaction rates. As a first-order rate process, tissue thermal damage is described using the Arrhenius damage integral (where Ω is the dimensionless factor defining irreversible thermal damage, A f (1/s) is the frequency factor, E x (J/mol) is the denaturation activation energy, R is the universal gas constant 8.314 (J/mol·K), and τ(s) is the LITT irradiation time. Therefore, the onset of irreversible thermal denaturation corresponds to the interstitial tissue temperature of 60°C-65°C, where Ω=1.
表1 目标脏器光学性质主要参数常量Table 1 Main parameter constants of optical properties of target organs
Figure PCTCN2022123856-appb-000008
Figure PCTCN2022123856-appb-000008
Figure PCTCN2022123856-appb-000009
Figure PCTCN2022123856-appb-000009
表1显示了目标脏器在980nm或1064nm下的光学性质的主要参数常量类型，假定其在LITT治疗期间是恒定的)：Table 1 shows the main parameter constant types for the optical properties of the target organ at 980 nm or 1064 nm, which are assumed to be constant during LITT treatment):
Figure PCTCN2022123856-appb-000010
Figure PCTCN2022123856-appb-000010
设定Λ和n eff是自由空间波长下基本核模的光栅周期和有效折射率，λ S受光栅周期热膨胀或收缩的温度变化和热光效应(n eff的热诱导变化)的影响，这使得FBG能够用作温度传感元件，结合前述原材料的FBG的制备工艺得到FBG传感器1404-1，这使得光纤芯的折射率得到周期性调制。周期性的核心索引调制产生核心模式，这些模式通过众多的索引边界反射或传输，并相互干扰。反过来，输入光束只在由一定相位匹配条件决定的特定波长处经历强反射。反射波长被称为FBG的布拉格波长(λ S)，相位匹配条件，称为布拉格条件。λ S的量化得出为： Assuming that Λ and n eff are the grating period and effective refractive index of the fundamental nuclear mode at the free space wavelength, λ S is affected by the temperature change of thermal expansion or contraction of the grating period and the thermo-optical effect (thermal-induced change of n eff ), which makes FBG can be used as a temperature sensing element. The FBG sensor 1404-1 is obtained by combining the preparation process of FBG with the aforementioned raw materials, which allows the refractive index of the optical fiber core to be periodically modulated. Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other. In turn, the input beam only experiences strong reflections at specific wavelengths determined by certain phase matching conditions. The reflected wavelength is called the Bragg wavelength (λ S ) of the FBG, and the phase matching condition is called the Bragg condition. The quantification of λ S is:
λ S＝2∧n eff，  (6) λ S =2∧n eff , (6)
ΔT＝T H-T 0，T 0和T H分别是应用于FBG的参考和高温。λ S0是T 0时FBG的布拉格波长，α ∧和α n分别是生产为FBG的单极光纤的热膨胀和热光学系数，由温度变化ΔT诱导的布拉格波长漂移Δλ S量化为： ΔT = T H - T 0 , T 0 and TH are the reference and high temperatures applied to the FBG, respectively. λ S0 is the Bragg wavelength of FBG at T 0 , α ∧ and α n are the thermal expansion and thermo-optical coefficients of the monopole fiber produced as FBG, respectively. The Bragg wavelength drift Δλ S induced by the temperature change ΔT is quantified as:
Figure PCTCN2022123856-appb-000011
Figure PCTCN2022123856-appb-000011
使用预先量化定义的S，Δλ S的测量将允许量化得出ΔT，即消融温度变化，根据上述公式(6)，FBG的热敏性S量化为： Using the pre-defined S, the measurement of Δλ S will allow the quantification of ΔT, i.e. the ablation temperature change. According to the above formula (6), the thermal sensitivity S of the FBG is quantified as:
Figure PCTCN2022123856-appb-000012
Figure PCTCN2022123856-appb-000012
因此根据以上算法，FBG传感器1404-1可实时监测LITT激光辐照期间的间质组织温度。Therefore, according to the above algorithm, the FBG sensor 1404-1 can monitor the interstitial tissue temperature during LITT laser irradiation in real time.
在应用FBG传感器1404-1进行LITT探针进行治疗或者辅助手术之前，根据公式(8)，需预先获得FBG的热敏性S FSG，并基于公式(7)的原则对Δλ S和ΔT之间的关系进行校准。 Before applying FBG sensor 1404-1 for LITT probe treatment or auxiliary surgery, according to formula (8), it is necessary to obtain the thermal sensitivity S FSG of FBG in advance, and calculate the relationship between Δλ S and ΔT based on the principle of formula (7) Perform calibration.
该校准需要在FBG测温校准模式下，温度控制器1406的控制下的温度范围(例如，-50℃到180℃，-40℃至150℃，-30℃至120℃，-20℃至100℃等)内，进行该静态校准。校准时系统包括终端1401、ASE激光器1402、环形器1403、FBG传感器1404-2、电信光谱分析仪1405、以及温度控制器1406。This calibration requires the temperature range under the control of the temperature controller 1406 in the FBG temperature measurement calibration mode (for example, -50°C to 180°C, -40°C to 150°C, -30°C to 120°C, -20°C to 100°C °C, etc.), perform this static calibration. During calibration, the system includes terminal 1401, ASE laser 1402, circulator 1403, FBG sensor 1404-2, telecommunications spectrum analyzer 1405, and temperature controller 1406.
FBG测温校准模式下，将FBG传感器1404-2置于可将温度控制在-40℃至150℃温度控制器1406。ASE激光器1402可以为超宽带ASE激光器，其宽带光通过环形器1403到达FBG传感器1404-2。然后FBG传感器1404-2的反射信号通过环形器1403进入电信光谱分析仪1405，用电信光谱分析仪1405监测FBG传感器1404-2的反射光谱。具体地，在特定温度范围内(例如，10℃-80℃，20℃-100℃，30℃-120℃)进行校准试验，每个温度间隔为10℃，持续5h。以便FBG的动态布拉格波长漂移Δλ S对应相应的温度控制器1406内温度变化ΔT。并根据另外的算法原理S FSG＝Δλ S/ΔT，测得S FSG≈0.0114nm/℃，既预先获得FBG的热敏性S FSG。则根据公式(8)通过Δλ S，终端1401可以得到实测温度。 In the FBG temperature measurement calibration mode, the FBG sensor 1404-2 is placed in the temperature controller 1406 that can control the temperature between -40°C and 150°C. The ASE laser 1402 may be an ultra-wideband ASE laser, and its broadband light reaches the FBG sensor 1404-2 through the circulator 1403. Then the reflection signal of the FBG sensor 1404-2 enters the telecommunications spectrum analyzer 1405 through the circulator 1403, and the telecommunications spectrum analyzer 1405 is used to monitor the reflection spectrum of the FBG sensor 1404-2. Specifically, the calibration test is performed within a specific temperature range (for example, 10°C-80°C, 20°C-100°C, 30°C-120°C), with each temperature interval being 10°C and lasting 5 hours. So that the dynamic Bragg wavelength drift Δλ S of the FBG corresponds to the corresponding temperature change ΔT in the temperature controller 1406 . And according to another algorithm principle S FSG = Δλ S /ΔT, S FSG ≈0.0114nm/°C is measured, which means that the thermal sensitivity S FSG of FBG is obtained in advance. Then according to formula (8) through Δλ S , the terminal 1401 can obtain the actual measured temperature.
图15是根据本说明书一些实施例所示的示例性OCT探针。Figure 15 is an exemplary OCT probe according to some embodiments of the present specification.
OCT探针1500具备长工作距离，适用于辅助LITT消融大尺寸目标对象(例如，癌化组织)。The OCT probe 1500 has a long working distance and is suitable for assisting LITT in ablating large-sized target objects (for example, cancerous tissue).
如图所示，所述OCT探针1500包括输入端口1501，第一透镜1502，第二透镜1504，光束偏转单元1506，弹簧扭力线圈1508，光学套管1510和填充体1512。第二透镜1504的两个端面分别与第一透镜1502和光束偏转单元1506通过特定材料，如钨、铱高温熔融而熔接，并进行火抛光，从而形成熔接面，使得第二透镜1504与第一透镜1502和光束偏转单元1506固定连接。As shown in the figure, the OCT probe 1500 includes an input port 1501, a first lens 1502, a second lens 1504, a beam deflection unit 1506, a spring torsion coil 1508, an optical sleeve 1510 and a filling body 1512. The two end surfaces of the second lens 1504 are respectively welded to the first lens 1502 and the beam deflection unit 1506 through high-temperature fusion of specific materials, such as tungsten and iridium, and are fire polished to form a welded surface, so that the second lens 1504 is connected to the first lens 1504 . The lens 1502 and the beam deflection unit 1506 are fixedly connected.
OCT设备的光源发出的光束经特定光路，例如，光纤滑环装置212、输入端口1501(例如，单模光纤)，进入所述OCT探针1500。所述输入端口1501被配置为将所述光源发出的光束输入至所述OCT探针1500。进入所述OCT探针1500的光束依次经过所述第一透镜1502，第二透镜1504，并经光束偏转单元1506，偏转出射所述OCT探针1500。出射所述OCT探针1500的光束可以用于照射所述目标对象。The light beam emitted by the light source of the OCT equipment enters the OCT probe 1500 through a specific optical path, such as the optical fiber slip ring device 212 and the input port 1501 (eg, single-mode optical fiber). The input port 1501 is configured to input the light beam emitted by the light source to the OCT probe 1500 . The light beam entering the OCT probe 1500 passes through the first lens 1502 and the second lens 1504 in sequence, and is deflected by the light beam deflection unit 1506 and exits the OCT probe 1500 . The light beam emerging from the OCT probe 1500 may be used to illuminate the target object.
所述第一透镜1502被配置为对入射所述OCT探针1500(第一透镜1502)的光束进行扩束。例如，入射光束为平行光束，第一透镜1502可以使所述平行光束扩束。扩束后的光束具有一定的发散角(又称扩束角)。所述第一透镜1502为圆柱状。The first lens 1502 is configured to expand the light beam incident on the OCT probe 1500 (first lens 1502). For example, the incident light beam is a parallel light beam, and the first lens 1502 can expand the parallel light beam. The expanded beam has a certain divergence angle (also called beam expansion angle). The first lens 1502 is cylindrical.
在一些实施例中，第一透镜1502为无芯透镜。所述无芯透镜的扩束角为2θ，其中θ为，例如，5°、10°、15°、20°、25°等。所述无芯透镜具有一定长度b。在一些实施例中，所述OCT探针1500的焦距及焦点光斑大小与所述无芯透镜的长度b相关。In some embodiments, first lens 1502 is a coreless lens. The beam expansion angle of the coreless lens is 2θ, where θ is, for example, 5°, 10°, 15°, 20°, 25°, etc. The coreless lens has a certain length b. In some embodiments, the focal length and focal spot size of the OCT probe 1500 are related to the length b of the coreless lens.
所述第二透镜1504设置于所述第一透镜1502的后级(后端)，出射所述第一透镜1502的光束入射所述第二透镜1504。所述第二透镜1504被配置为对出射所述第一透镜1502的光束进行聚焦，产生一定焦距的出射光谱。在一些实施例中，所述第二透镜1504也可以对出射所述第一透镜的光束进行消色散。The second lens 1504 is disposed at the rear stage (rear end) of the first lens 1502 , and the light beam emitted from the first lens 1502 enters the second lens 1504 . The second lens 1504 is configured to focus the light beam exiting the first lens 1502 to generate an exit spectrum with a certain focal length. In some embodiments, the second lens 1504 can also achromatically disperse the light beam exiting the first lens.
在一些实施例中，所述第二透镜1504可以为微平凸球面柱透镜。所述微平凸球面柱透镜沿透镜轴向(例如，图中光束传播的方向)具有始端和末端。此处所述始端为光束入射的端面，所述末端为光束出射的端面。如图所示，所述微平凸球面柱透镜的始端为平面，末端为凸球面。始端和末端之间的部分为圆柱体。所述圆柱体具有一定的柱面直径(即圆柱体的横截面直径)。所述柱面直径为，例如，500μm、520μm、540μm、560μm、580μm、600μm、620μm等。在一些实施例中，所述柱面直径为560μm，此时可以保障光束完整通过。而大于或小于560μm均会折损光路性能(例如，低于560μm将导致扩散光路无法全面被OCT探针1500机械兼容，造成严重的插入损耗和成像带宽损失)。所述微平凸球面柱透镜的末端凸球面的光学曲率r为，例如，-1.5mm、-1.6mm、-1.7mm、-1.8mm、-1.9mm、-2mm、-2.1mm等。在一些实施例中，所述微平凸球面柱透镜的末端凸球面的光学曲率r为-1.8mm。其中，-1.8mm的曲率是保障OCT探针1500超过1cm有效工作距离的关键，否则焦距将会内移降低工作距离以及扩大光斑、降低横向分辨率，降低成像品质。In some embodiments, the second lens 1504 may be a micro-plano-convex spherical cylindrical lens. The micro-plano-convex spherical cylindrical lens has a starting end and an end along the lens axis (for example, the direction of light beam propagation in the figure). The starting end here is the end surface where the light beam is incident, and the end is the end surface where the light beam is emitted. As shown in the figure, the starting end of the micro-plano-convex spherical cylindrical lens is a flat surface and the end is a convex spherical surface. The part between the beginning and the end is a cylinder. The cylinder has a certain cylinder diameter (ie, the cross-sectional diameter of the cylinder). The cylinder diameter is, for example, 500 μm, 520 μm, 540 μm, 560 μm, 580 μm, 600 μm, 620 μm, etc. In some embodiments, the diameter of the cylinder is 560 μm, which can ensure that the light beam passes completely. Anything greater than or less than 560μm will compromise the optical path performance (for example, less than 560μm will cause the diffused optical path to be unable to be fully mechanically compatible with the OCT probe 1500, resulting in serious insertion loss and loss of imaging bandwidth). The optical curvature r of the terminal convex spherical surface of the micro plano-convex spherical cylindrical lens is, for example, -1.5mm, -1.6mm, -1.7mm, -1.8mm, -1.9mm, -2mm, -2.1mm, etc. In some embodiments, the optical curvature r of the terminal convex spherical surface of the micro plano-convex spherical cylindrical lens is -1.8 mm. Among them, the -1.8mm curvature is the key to ensuring that the OCT probe 1500 exceeds the effective working distance of 1cm. Otherwise, the focal length will shift inward to reduce the working distance, expand the spot, reduce lateral resolution, and reduce imaging quality.
所述微平凸球面柱透镜的所采用的材料为，例如，N-LAF3、SF11、N-SF11等光学材料。在一些实施例中，所述微平凸球面柱透镜的所采用的材料为N-LAF3。所述微平凸球面柱透镜具有一定折射率n。所述折射率n为，例如，1.3、1.4、1.5、1.6、1.7、1.8等。The materials used in the micro plano-convex spherical cylindrical lens are, for example, N-LAF3, SF11, N-SF11 and other optical materials. In some embodiments, the material used in the micro plano-convex spherical cylindrical lens is N-LAF3. The micro-plano-convex spherical cylindrical lens has a certain refractive index n. The refractive index n is, for example, 1.3, 1.4, 1.5, 1.6, 1.7, 1.8, etc.
在一些实施例中，所述第二透镜1504的始端(即光束入射端面)为抛光面，且具有一定角度。此处所述角度为所述第二透镜1504的轴线的垂直面与所述第二透镜1504的始端端面之间的夹角。所述角度为，例如，0°、2°、4°、6°、8°、10°等。在一些实施例中，所述角度为0°或8°。所述角度为0°时可以在熔接面火抛光后增加力学应力性能；所述角度为8°时可以显著减少透镜熔接面的TIR污染值，减少插入损耗。In some embodiments, the starting end of the second lens 1504 (ie, the beam incident end surface) is a polished surface and has a certain angle. The angle here is the angle between the vertical plane of the axis of the second lens 1504 and the starting end surface of the second lens 1504 . The angles are, for example, 0°, 2°, 4°, 6°, 8°, 10°, etc. In some embodiments, the angle is 0° or 8°. When the angle is 0°, the mechanical stress performance can be increased after fire polishing of the welding surface; when the angle is 8°, the TIR pollution value of the lens welding surface can be significantly reduced and the insertion loss is reduced.
所述光束偏转单元1506设置于所述第二透镜的后级(后端)，出射所述第二透镜1504的光束入射所述光束偏转单元1506。所述光束偏转单元1506被配置为对出射所述第二透镜1504的光束进行偏转，偏转后的光束出射所述OCT探针1500。The beam deflection unit 1506 is disposed at the rear stage (rear end) of the second lens, and the beam exiting the second lens 1504 enters the beam deflection unit 1506 . The beam deflection unit 1506 is configured to deflect the light beam that exits the second lens 1504 , and the deflected light beam exits the OCT probe 1500 .
在一些实施例中，所述光束偏转单元1506包括圆柱形纤芯和位于纤芯外周的硬质包层。所述光束偏转单元1506包括斜切端面，所述斜切端面涂覆有金属镀层。在一些实施例中，所述光束偏转单元1506可以类似于图7所述的LITT侧向消融探针700。具体地，所述光束偏转单元1506包括主体、连接面和镀层。所述主体包括纤芯和位于纤芯外周的硬质包层。所述纤芯由纯二氧化硅材料制成。所述硬质包层由技术增强型包层二氧化硅(TECS) 材料制成。所述主体的端面具有一定倾角，即为所述斜切端面，此时，所述主体的端面与主体的轴线呈一定夹角，所述夹角为0-90°，且不含该范围的端点。所述连接面为所述斜切端面与镀层之间的连接界面。通过对所述斜切端面进行光洁化，形成所述连接面。所述连接面涂覆所述镀层(例如，贵金属镀层)。所述贵金属可以包括，例如，金、银和铂族金属。所述镀层可以通过在连接面的表面进行，例如，磁控溅射镀膜形成。在一些实施例中，所述镀层与所述主体的轴线之间的角度为，例如，35°、37°、39°、41°、43°、45°、47°、49°等。In some embodiments, the beam deflection unit 1506 includes a cylindrical core and a hard cladding located around the core. The beam deflection unit 1506 includes a beveled end surface, and the beveled end surface is coated with a metal plating layer. In some embodiments, the beam deflection unit 1506 may be similar to the LITT lateral ablation probe 700 described in FIG. 7 . Specifically, the beam deflection unit 1506 includes a main body, a connection surface and a coating. The main body includes a fiber core and a hard cladding located on the periphery of the fiber core. The core is made of pure silica material. The hard cladding is made of Technology Enhanced Cladding Silica (TECS) material. The end face of the main body has a certain inclination angle, which is the beveled end face. At this time, the end face of the main body forms a certain angle with the axis of the main body. The included angle is 0-90°, and does not include this range. endpoint. The connection surface is the connection interface between the chamfered end surface and the plating layer. The connecting surface is formed by smoothing the chamfered end surface. The connection surface is coated with the plating layer (for example, a noble metal plating layer). The precious metals may include, for example, gold, silver, and platinum group metals. The coating can be formed on the surface of the connection surface by, for example, magnetron sputtering coating. In some embodiments, the angle between the coating and the axis of the body is, for example, 35°, 37°, 39°, 41°, 43°, 45°, 47°, 49°, etc.
在一些实施例中，所述光束偏转单元1506的截断轴向柱体具有一定长度。所述截断轴向柱体即为所述光束偏转单元1506的光束入射端面与所述斜切端面的斜切点之间的柱体。所述斜切点为所述斜切端面上距离所述光束偏转单元1506的光束入射端面最近的点。所述截断轴向柱体长度为，例如，2μm、5μm、8μm、10μm等。在一些实施例中，所述截断轴向柱体长度为5μm，此时所述光束偏转单元1506的光谱偏转效果较好。In some embodiments, the truncated axial cylinder of the beam deflection unit 1506 has a certain length. The truncated axial cylinder is the cylinder between the beam incident end surface of the beam deflection unit 1506 and the bevel point of the beveled end surface. The bevel point is the point on the bevel end surface that is closest to the beam incident end surface of the beam deflection unit 1506 . The cut-off axial cylinder length is, for example, 2 μm, 5 μm, 8 μm, 10 μm, etc. In some embodiments, the length of the truncated axial cylinder is 5 μm, in which case the spectral deflection effect of the beam deflection unit 1506 is better.
所述弹簧扭力线圈1508设置于所述OCT探针1500的前端。示例性地，所述弹簧扭力线圈1508的一端抵接于所述第二透镜1504的始端上。所述弹簧扭力线圈1508通过其可拉升、压缩及扭转的性能，为所述OCT探针1500提供转动扭力支持。The spring torsion coil 1508 is disposed at the front end of the OCT probe 1500 . For example, one end of the spring torsion coil 1508 is in contact with the starting end of the second lens 1504 . The spring torsion coil 1508 provides rotational torsion support for the OCT probe 1500 through its properties of lifting, compressing and twisting.
光学套管1510用于容纳所述弹簧扭力线圈1508、第一透镜1502、第二透镜1504及光束偏转单元1506。在一些实施例中，光学套管1510为管状光学元件，例如，管状光学玻璃。所述弹簧扭力线圈1508、第一透镜1502、第二透镜1504及光束偏转单元1506依次设置于所述光学套管1510中。同时，光学套管1510具有光透过性。经所述光束偏转单元1506出射的光束经所述光学套管1510，出射所述OCT探针1500。The optical sleeve 1510 is used to accommodate the spring torsion coil 1508, the first lens 1502, the second lens 1504 and the beam deflection unit 1506. In some embodiments, optical tube 1510 is a tubular optical element, such as tubular optical glass. The spring torsion coil 1508, the first lens 1502, the second lens 1504 and the beam deflection unit 1506 are arranged in the optical tube 1510 in sequence. At the same time, the optical sleeve 1510 has light transmittance. The light beam emitted through the beam deflection unit 1506 passes through the optical sleeve 1510 and exits the OCT probe 1500.
填充体1512填充于所述光学套管1510内部。在一些实施例中，填充体1512为光学胶，填充后经一定时间后发生固化。通过将所述填充体1512注入所述光学套管1510内部，所述填充体1512可以填充于所述第一透镜1502、第二透镜1504、光束偏转单元1506及所述光学套管1510之间的缝隙中，从而可以使所述第一透镜1502、第二透镜1504及光束偏转单元1506相对于所述光学套管1510固定。在一些实施例中，所述填充体1512的折射率远小于所述第二透镜(例如，所述微平凸球面柱透镜)的折射率，避免对光束在所述OCT探针1500中的传播产生影响。The filling body 1512 is filled inside the optical sleeve 1510 . In some embodiments, the filling body 1512 is optical glue, which solidifies after a certain period of time after filling. By injecting the filling body 1512 into the optical sleeve 1510 , the filling body 1512 can be filled between the first lens 1502 , the second lens 1504 , the beam deflection unit 1506 and the optical sleeve 1510 In the gap, the first lens 1502, the second lens 1504 and the beam deflection unit 1506 can be fixed relative to the optical tube 1510. In some embodiments, the refractive index of the filling body 1512 is much smaller than the refractive index of the second lens (for example, the micro-plano-convex spherical cylindrical lens) to avoid affecting the propagation of the light beam in the OCT probe 1500 Make an impact.
在一些实施例中，在忽略所述光束偏转单元1506的截断轴向柱体长度的影响下，假定OCT探针1500的焦距为z 0，焦点光斑直径为2ω 0，设OCT探针1500出射光谱任意长度为z，z对应处的光斑直径为2ω。因此OCT探针1500的ABCD光学高斯传输矩阵T可表示为： In some embodiments, while ignoring the influence of the truncated axial cylinder length of the beam deflection unit 1506, assuming that the focal length of the OCT probe 1500 is z 0 and the focal spot diameter is 2ω 0 , it is assumed that the emission spectrum of the OCT probe 1500 Any length is z, and the spot diameter corresponding to z is 2ω. Therefore, the ABCD optical Gaussian transmission matrix T of the OCT probe 1500 can be expressed as:
Figure PCTCN2022123856-appb-000013
Figure PCTCN2022123856-appb-000013
OCT探针1500出射光谱任意长度为z处的高斯传输矩M可表示为公式：The Gaussian transmission moment M at any length z of the OCT probe 1500 emission spectrum can be expressed as the formula:
Figure PCTCN2022123856-appb-000014
Figure PCTCN2022123856-appb-000014
同时定义光源中心波数为k 0，光谱带宽范围中不同遍历i下的波长为λ，不同b值下的探针焦距为： At the same time, the central wave number of the light source is defined as k 0 , the wavelength under different traversals i in the spectral bandwidth range is λ, and the probe focal length under different b values is:
Figure PCTCN2022123856-appb-000015
Figure PCTCN2022123856-appb-000015
不同b值下的焦点光斑半径为：The focus spot radius under different b values is:
Figure PCTCN2022123856-appb-000016
Figure PCTCN2022123856-appb-000016
由此可知，通过调整所述第一透镜1502(例如，无芯透镜)的长度，可以调整OCT探针1500的焦距和焦点光斑尺寸，由此改变所述OCT探针1500的工作距离，使其可以适用于大尺寸组织的病理成像。It can be seen from this that by adjusting the length of the first lens 1502 (for example, a coreless lens), the focal length and focus spot size of the OCT probe 1500 can be adjusted, thereby changing the working distance of the OCT probe 1500 to make it Can be applied to pathological imaging of large-sized tissues.
图16是根据本说明书一些实施例所示的制备FBG传感器的示意图。Figure 16 is a schematic diagram of preparing an FBG sensor according to some embodiments of this specification.
在本实施例中，所述FBG传感器是通过FBG辐照设备1600对特殊制备的原材料进行辐照而得到。所述特殊制备的原材料须满足特定的参数条件。所述参数条件如前所述，此处不再赘述。所述FBG辐照设备1600包括终端1601，激光器控制器1602，激光器1603，光束校正装置1604-1和1604-2，狭缝光阑1605，紫外镀膜透镜1606，相位掩膜1607，滑轨1609，固定器件1610，运动驱动器1611，和运动驱动控制器1612。In this embodiment, the FBG sensor is obtained by irradiating specially prepared raw materials through FBG irradiation equipment 1600 . The specially prepared raw materials must meet specific parameter conditions. The parameter conditions are as mentioned above and will not be repeated here. The FBG irradiation equipment 1600 includes a terminal 1601, a laser controller 1602, a laser 1603, beam correction devices 1604-1 and 1604-2, a slit diaphragm 1605, a UV coating lens 1606, a phase mask 1607, and a slide rail 1609. Fixation device 1610, motion driver 1611, and motion drive controller 1612.
其中，终端1601连接并控制激光器控制器1602和运动驱动控制器1612。终端1601可以为，例如，计算机。激光器控制器1602连接并控制激光器1603发射激光。激光器1603可以是具有特定特征波长(例如，248nm)的准分子脉冲激光器。对于激光器1603，其产生激光的功率可以为，例如，8W，10W，12W，15W等；其脉冲频率可以为，例如，90Hz，100Hz，120Hz等；其脉冲能量可以为，例如，100mJ，120mJ，140mJ等。Among them, the terminal 1601 connects and controls the laser controller 1602 and the motion drive controller 1612. Terminal 1601 may be, for example, a computer. The laser controller 1602 connects and controls the laser 1603 to emit laser light. Laser 1603 may be an excimer pulsed laser with a specific characteristic wavelength (eg, 248 nm). For the laser 1603, the power of the laser it generates can be, for example, 8W, 10W, 12W, 15W, etc.; its pulse frequency can be, for example, 90Hz, 100Hz, 120Hz, etc.; its pulse energy can be, for example, 100mJ, 120mJ, 140mJ etc.
相应地，激光器1603产生的激光为通量(能量密度)几乎一致的平顶激光光束，所述激光光束的光斑出射表征为矩形平顶，其中央波长为，例如，248nm；其脉冲持续时间为，例如，10ns，12ns，15ns，20ns等；所述矩形平顶为，例如，4×1mm 2，6×1.5mm 2，10×3mm 2等；其发散角为，例如，2×1mrad 2，3×2mrad 2，4×2mrad 2等。 Correspondingly, the laser generated by the laser 1603 is a flat-top laser beam with almost uniform flux (energy density). The spot emission of the laser beam is characterized by a rectangular flat-top, and its central wavelength is, for example, 248 nm; its pulse duration is , for example, 10ns, 12ns, 15ns, 20ns, etc.; the rectangular flat top is, for example, 4×1mm 2 , 6×1.5mm 2 , 10×3mm 2 , etc.; its divergence angle is, for example, 2×1mrad 2 , 3×2mrad 2 , 4×2mrad 2 , etc.
光束校正装置1604-1和1604-2用于对光束进行偏折，并进行光路矫正。在本实施例中，光束校正装置1604-1和1604-2均为248nm特征波长准分子激光45°线镜，用以对激光器1603产生的激光进行45°偏转，并进行光路矫正。The beam correction devices 1604-1 and 1604-2 are used to deflect the beam and correct the optical path. In this embodiment, the beam correction devices 1604-1 and 1604-2 are both 248 nm characteristic wavelength excimer laser 45° line mirrors, used to deflect the laser light generated by the laser 1603 at 45° and perform optical path correction.
狭缝光阑1605用于限制光束在特定方向的传播。狭缝光阑1605的尺寸(即狭缝的宽度)为，例如，2-6mm。在一些实施例中，狭缝光阑1605的尺寸为2mm。在一些实施例中，狭缝光阑1605的尺寸为3mm。在一些实施例中，狭缝光阑1605的尺寸为4.5mm。在一些实施例中，狭缝光阑1605的尺寸为6mm。在本实施例中，狭缝光阑1605为4.5mm宽度可调的机械狭缝装置。The slit diaphragm 1605 is used to limit the propagation of light beams in specific directions. The size of the slit aperture 1605 (ie, the width of the slit) is, for example, 2-6 mm. In some embodiments, the size of slit aperture 1605 is 2 mm. In some embodiments, slit aperture 1605 measures 3 mm. In some embodiments, slit aperture 1605 measures 4.5 mm. In some embodiments, slit aperture 1605 measures 6 mm. In this embodiment, the slit diaphragm 1605 is a mechanical slit device with an adjustable width of 4.5 mm.
紫外镀膜透镜1606用于对紫外区域的激光光束进行聚焦。在本实施例中，紫外镀膜透镜1606可以为紫外镀膜熔融石英平凸圆柱透镜。所述紫外镀膜熔融石英平凸圆柱透镜可以将光束聚焦(焦距为，例如，150mm，200mm，250mm等)至相位掩膜1607。所述紫外镀膜熔融石英平凸圆柱透镜的特征波长为100-600nm。在一些实施例中，所述紫外镀膜熔融石英平凸圆柱透镜的特征波长为200-500nm。在一些实施例中，所述紫外镀膜熔融石英平凸圆柱透镜的特征波长为245-440nm。The ultraviolet coated lens 1606 is used to focus the laser beam in the ultraviolet region. In this embodiment, the UV-coated lens 1606 may be a UV-coated fused silica plano-convex cylindrical lens. The UV-coated fused silica plano-convex cylindrical lens can focus the light beam (focal length is, for example, 150mm, 200mm, 250mm, etc.) to the phase mask 1607. The characteristic wavelength of the UV-coated fused silica plano-convex cylindrical lens is 100-600nm. In some embodiments, the characteristic wavelength of the UV-coated fused silica plano-convex cylindrical lens is 200-500 nm. In some embodiments, the characteristic wavelength of the UV-coated fused silica plano-convex cylindrical lens is 245-440 nm.
相位掩膜1607设置于原材料1608前方。经激光光束照射，可以在原材料1608上形成条带状光斑。在本实施例中，所述相位掩膜1607为紫外辐照248nm特征波长超带宽(例如，1460-1600nm)相位掩膜。所述条带状光斑的宽度为，例如，10mm，15mm，20mm，25mm等；高度为，例如，28μm，32.4μm，40μm，50μm等。The phase mask 1607 is disposed in front of the raw material 1608. After being irradiated with a laser beam, strip-shaped spots can be formed on the raw material 1608. In this embodiment, the phase mask 1607 is an ultraviolet irradiation 248nm characteristic wavelength ultra-bandwidth (for example, 1460-1600nm) phase mask. The width of the strip-shaped light spot is, for example, 10 mm, 15 mm, 20 mm, 25 mm, etc.; the height is, for example, 28 μm, 32.4 μm, 40 μm, 50 μm, etc.
运动驱动控制器1612连接并控制运动驱动器1611，以驱动固定器件1610运动，例如，平移和/或旋转。The motion drive controller 1612 is connected to and controls the motion driver 1611 to drive the fixation device 1610 to move, for example, translation and/or rotation.
通过FBG辐照设备1600对特殊制备的原材料进行辐照，制备FBG传感器的过程包括如下步骤：The specially prepared raw materials are irradiated by the FBG irradiation equipment 1600. The process of preparing the FBG sensor includes the following steps:
S16-1：将原材料1608两端分别固定于滑轨1609和固定器件1610。所述固定器件1610固定连接于运动驱动器1611。固定器件1610可以是夹具。所述夹具可以夹持固定原材料1608的一端。S16-1: Fix both ends of the raw material 1608 to the slide rail 1609 and the fixing device 1610 respectively. The fixing device 1610 is fixedly connected to the motion driver 1611. Fixing device 1610 may be a clamp. The clamp may clamp and secure one end of the raw material 1608 .
S16-2：由激光器控制器1602控制激光器1603发射激光，所述激光依次经过上述光束校正装置1604-1和1604-2，狭缝光阑1605，紫外镀膜透镜1606和相位掩膜1607后，在所述原材料1608表面产生条带状光斑。S16-2: The laser controller 1602 controls the laser 1603 to emit laser. After the laser passes through the above-mentioned beam correction devices 1604-1 and 1604-2, the slit diaphragm 1605, the ultraviolet coating lens 1606 and the phase mask 1607, Strip-shaped light spots are generated on the surface of the raw material 1608.
S16-3：由运动驱动控制器1612控制运动驱动器1611，驱动所述原材料1608运动，在所述原材料1608运动过程中，通过所述激光照射所述原材料1608，从而形成所述FBG传感器。S16-3: The motion drive controller 1612 controls the motion driver 1611 to drive the raw material 1608 to move. During the movement of the raw material 1608, the laser irradiates the raw material 1608 to form the FBG sensor.
所述固定器件1610固定连接于运动驱动器1611。当运动驱动控制器1612控制运动驱动器1611，驱动所述固定器件1610运动时，所述原材料1608也随之运动(平移、旋转等)。在所述原材料1608运动过程中，激光经相位掩膜1607形成的条带状光斑在原材料1608表面进行辐照，使得光纤芯的折射率得到周期性调制。周期性的核心索引调制产生核心模式，这些模式通过众多的索引边界反射或传输，并相互干扰。反过来，输入光束只在由一定相位匹配条件决定的特定波长处经历强反射，反射波长被称为FBG的布拉格波长，相位匹配条件，称为布拉格条件，最终形成所述FBG传感器。The fixing device 1610 is fixedly connected to the motion driver 1611. When the motion drive controller 1612 controls the motion driver 1611 to drive the fixing device 1610 to move, the raw material 1608 also moves (translation, rotation, etc.) accordingly. During the movement of the raw material 1608, the strip-shaped spot formed by the laser through the phase mask 1607 is irradiated on the surface of the raw material 1608, so that the refractive index of the optical fiber core is periodically modulated. Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other. In turn, the input beam only experiences strong reflection at a specific wavelength determined by a certain phase matching condition, called the Bragg wavelength of the FBG, which ultimately forms the FBG sensor.
图17是根据本说明书一些实施例所示的医学治疗装置的示意图。Figure 17 is a schematic diagram of a medical treatment device according to some embodiments of the present specification.
在一些实施例中，医学治疗装置1700可以是将医学治疗系统100中(本地或远程的)各设备及部件进行集成的装置。如图所示，医学治疗装置1700可以包括MRI设备(图中未示出)、LITT设备(图中未示出)、测温设备(图中未示出)、OCT设备(图中未示出)、控制设备1710、接口平台集线控制模组1720、驱动组件1730、探针组1740、温度反馈控制单元1750、激光剂量控制单元1760、衰减器调节控制单元1770、衰减器调节单元1780以及激光功率衰减器1790。In some embodiments, the medical treatment device 1700 may be a device that integrates various devices and components in the medical treatment system 100 (local or remote). As shown in the figure, the medical treatment device 1700 may include MRI equipment (not shown in the figure), LITT equipment (not shown in the figure), temperature measurement equipment (not shown in the figure), OCT equipment (not shown in the figure) ), control device 1710, interface platform line control module 1720, driving component 1730, probe group 1740, temperature feedback control unit 1750, laser dose control unit 1760, attenuator adjustment control unit 1770, attenuator adjustment unit 1780 and laser Power Attenuator 1790.
MRI设备用于对包括目标对象(例如，癌症病灶)的特定区域进行成像，生成MRI图像。所述MRI图像可以是实时MRI图像，也可以是非实时MRI图像。所述MRI图像可以包括三维图像或多个二维图像(例如，横断面、冠状面及矢状面图像)，表征所述目标对象在三维空间中的信息(例如，位置和尺寸等)。所述MRI图像提供的目标对象在三维空间中的信息可以用于治疗前，对探针组1740的LITT探针、OCT探针和/或测温设备的测温元件经过人体组织到达所述目标对象处的路径进行规划(简称入针规划)。所述MRI图像提供的目标对象在三维空间 中的信息也可以用于治疗过程中，引导所述LITT探针、OCT探针和/或测温元件按照规划的路径进入人体组织，并到达所述目标对象处(简称入针引导)。在一些实施例中，所述MRI图像可以显示于终端(例如，终端150)。用户，如医生，可以通过终端(例如，终端150上的触摸屏、鼠标、键盘等物理元件)，基于所述MRI图像，进行LITT探针和/或测温元件的入针规划和入针引导。在一些实施例中，系统也可以自动基于所述MRI图像，进行LITT探针和/或测温元件的入针规划和入针引导。MRI equipment is used to image a specific area including a target object (for example, a cancer lesion) to generate an MRI image. The MRI image may be a real-time MRI image or a non-real-time MRI image. The MRI image may include a three-dimensional image or multiple two-dimensional images (eg, cross-sectional, coronal, and sagittal images), representing information (eg, position and size, etc.) of the target object in the three-dimensional space. The information about the target object in the three-dimensional space provided by the MRI image can be used before treatment. The LITT probe, the OCT probe and/or the temperature measurement element of the temperature measurement device of the probe set 1740 pass through the human tissue to reach the target. The path at the object is planned (referred to as needle entry planning). The information of the target object in the three-dimensional space provided by the MRI image can also be used in the treatment process to guide the LITT probe, OCT probe and/or temperature measurement element to enter the human tissue according to the planned path and reach the Target object (referred to as needle insertion guide). In some embodiments, the MRI image may be displayed on a terminal (eg, terminal 150). A user, such as a doctor, can perform needle insertion planning and needle insertion guidance of the LITT probe and/or temperature measurement element based on the MRI image through a terminal (for example, a touch screen, a mouse, a keyboard and other physical components on the terminal 150). In some embodiments, the system can also automatically perform needle insertion planning and needle insertion guidance for the LITT probe and/or temperature measurement element based on the MRI image.
在一些实施例中，MRI设备还可以对包括所述目标对象的特定区域进行磁共振热成像，生成热图像。所述热图像可以与所述MRI图像进行配准，以同时表示所述包含目标对象的特定区域的解剖结构信息以及相应位置的温度变化信息。In some embodiments, the MRI equipment can also perform magnetic resonance thermography on a specific area including the target object to generate a thermal image. The thermal image may be registered with the MRI image to simultaneously represent the anatomical structure information of the specific region containing the target object and the temperature change information of the corresponding location.
LITT设备用于产生激光，并利用激光的热效应，对目标对象进行治疗。LITT设备包括激光器，LITT探针(例如，LITT侧向消融探针、LITT周向消融探针)，以及连接所述激光器与所述LITT探针的通道(如光纤)及接口。在一些实施例中，所述激光器可以包括可调谐激光二极管和/或不可调谐激光二极管。所述可调谐激光二极管的激光功率在特定范围内，例如，0-500W，0-250W，0-50W，0-10W，1-8W等，可调谐。所述不可调谐激光二极管的激光功率为特定数值，例如，1W，3W，5W，8W，10W，12W，15W，20W，30W，60W，100W等。所述激光具有一定的特征波长，例如，840nm，980nm，1064nm，1300nm等。LITT equipment is used to generate laser light and use the thermal effect of the laser to treat the target object. The LITT device includes a laser, a LITT probe (eg, a LITT lateral ablation probe, a LITT circumferential ablation probe), and a channel (such as an optical fiber) and interface connecting the laser and the LITT probe. In some embodiments, the laser may include a tunable laser diode and/or a non-tunable laser diode. The laser power of the tunable laser diode is tunable within a specific range, such as 0-500W, 0-250W, 0-50W, 0-10W, 1-8W, etc. The laser power of the non-tunable laser diode is a specific value, for example, 1W, 3W, 5W, 8W, 10W, 12W, 15W, 20W, 30W, 60W, 100W, etc. The laser has certain characteristic wavelengths, such as 840nm, 980nm, 1064nm, 1300nm, etc.
测温装置包括测温元件。所述测温元件用于对所述目标对象或其边缘上特定位置(例如，所述目标对象边缘上距离所述LITT探针最远的位置)进行测温，以确定整个目标对象范围内的组织温度，保证治疗效果。所述LITT探针和所述测温元件之间的距离小于所述目标对象的尺寸。在一些实施例中，所述目标对象的边缘是非规则形状。所述目标对象可以被等效为圆形。例如，可以确定所述目标对象的最小外接圆，以作为所述目标对象的等效圆。所述目标对象的尺寸即为，例如，所述等效圆的直径。关于测温元件以及所述LITT探针的位置设定可以参照本说明书其他附图(例如，图20)及其描述，此处不再赘述。The temperature measuring device includes a temperature measuring element. The temperature measurement element is used to measure the temperature of the target object or a specific position on its edge (for example, the position on the edge of the target object farthest from the LITT probe) to determine the temperature within the entire target object range. Tissue temperature to ensure treatment effect. The distance between the LITT probe and the temperature measuring element is smaller than the size of the target object. In some embodiments, the edges of the target object are irregularly shaped. The target object may be equivalent to a circle. For example, the smallest circumscribed circle of the target object may be determined as the equivalent circle of the target object. The size of the target object is, for example, the diameter of the equivalent circle. Regarding the position setting of the temperature measurement element and the LITT probe, reference can be made to other drawings (for example, FIG. 20 ) and their descriptions in this specification, and will not be described again here.
测温元件可以包括热电偶(如K型热电偶)、LITT光子测温探针等。在本实施例中，所述测温元件可以是LITT光子测温探针。所述LITT光子测温探针可以包括FBG测温探针。所述FBG测温探针包括使用特殊原材料制备的光纤，其经过特定波长范围(例如，240-244nm，244-248nm，248-252nm，252-256nm等)的紫外光照射，使得光纤芯的折射率得到周期性调制。周期性的核心索引调制产生核心模式，这些模式通过众多的索引边界反射或传输，并相互干扰。反过来，输入光束只在由一定相位匹配条件决定的特定波长处经历强反射，反射波长被称为FBG的布拉格波长，相位匹配条件，称为布拉格条件，最终形成FBG测温探针。所述FBG测温探针可用于实时监测激光消融辐照期间的特定位置处的间质组织。Temperature measurement elements can include thermocouples (such as K-type thermocouples), LITT photon temperature measurement probes, etc. In this embodiment, the temperature measurement element may be a LITT photon temperature measurement probe. The LITT photon temperature measurement probe may include an FBG temperature measurement probe. The FBG temperature measurement probe includes an optical fiber prepared using special raw materials, which is irradiated with ultraviolet light in a specific wavelength range (for example, 240-244nm, 244-248nm, 248-252nm, 252-256nm, etc.), causing the fiber core to refract The rate is periodically modulated. Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other. In turn, the input beam only experiences strong reflection at a specific wavelength determined by certain phase matching conditions. The reflected wavelength is called the Bragg wavelength of the FBG. The phase matching condition, called the Bragg condition, ultimately forms the FBG temperature measurement probe. The FBG thermometric probe can be used for real-time monitoring of interstitial tissue at specific locations during laser ablation irradiation.
OCT设备基于生物结构的透光性，探测生物组织的反射、散射等信号，并将其转换成电信号，生成OCT图像。所述OCT图像为实时OCT图像，也可以是非实时OCT图像。OCT设备包括光源、OCT探针、干涉部件以及连接各部件的光纤及接口。所述光源采用低相干光源，以提高成像的纵向分辨率。在本实施例中，所述OCT设备可以是双模OCT，其光源可以产生两种不同参数(带宽、中央波长)的光信号。示例性地，双模OCT采用超过160nm带宽840nm中央波长，以及超过100nm扫频范围1300nm中央波长的光信号。双模OCT可以提供接近1μm分辨率、cm级深度的病理成像，以便对消融病理以及细胞凋亡的实际形态做实时病理成像，进而进行病理评价。Based on the light transmittance of biological structures, the OCT device detects the reflection, scattering and other signals of biological tissues, converts them into electrical signals, and generates OCT images. The OCT image is a real-time OCT image, or a non-real-time OCT image. The OCT device includes a light source, an OCT probe, an interference component, and an optical fiber and an interface connecting the components. The light source uses a low-coherence light source to improve the longitudinal resolution of the imaging. In this embodiment, the OCT device can be a dual-mode OCT, and its light source can generate optical signals with two different parameters (bandwidth, central wavelength). Exemplarily, the dual-mode OCT uses an optical signal with a bandwidth of more than 160nm and a central wavelength of 840nm, and a sweep range of more than 100nm and a central wavelength of 1300nm. Dual-mode OCT can provide pathological imaging with a resolution close to 1μm and a depth of cm, so as to perform real-time pathological imaging of the actual morphology of ablation pathology and cell apoptosis, and then perform pathological evaluation.
在一些实施例中，探针组1740包括所述LITT设备的LITT光子消融探针1742和测温设备的LITT光子测温探针1744。在一些实施例中，上述LITT探针(例如，LITT侧向消融探针、LITT周向消融探针)和OCT探针可以集成于一体，形成诊断治疗一体化的集成探针(后续简称为集成探针)。LITT光子消融探针1742可以是所述集成探针。LITT光子测温探针1744与LITT光子消融探针1742相互独立(例如，具有独立结构并且各自独立控制)。在本实施例中，LITT光子消融探针1742和测温设备的LITT光子测温探针1744相对于所述目标对象，设置于不同位置。关于LITT光子消融探针1742和LITT光子测温探针1744的具体结构及位置设置，可以参照本申请中其他附图(例如，图18-20)及其描述，此处不再赘述。In some embodiments, the probe set 1740 includes the LITT photon ablation probe 1742 of the LITT device and the LITT photon thermometry probe 1744 of the temperature measurement device. In some embodiments, the above-mentioned LITT probe (for example, LITT lateral ablation probe, LITT circumferential ablation probe) and OCT probe can be integrated into one body to form an integrated probe integrating diagnosis and treatment (hereinafter referred to as integrated probe for short). probe). LITT photon ablation probe 1742 may be the integrated probe. The LITT photon temperature measurement probe 1744 and the LITT photon ablation probe 1742 are independent of each other (eg, have independent structures and are independently controlled). In this embodiment, the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 of the temperature measurement device are arranged at different positions relative to the target object. Regarding the specific structure and position setting of the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744, reference may be made to other drawings in this application (for example, Figures 18-20) and their descriptions, which will not be described again here.
控制设备1710可以用于对医学治疗装置1700的一个或多个设备或部件进行控制，执行相应的操作。控制设备1710可以基于受控制的设备或部件及需要执行的操作，生成相应的指令。所述指令以电信号的形式，传达至对应的设备或部件，使该设备或部件执行相应的操作。所述控制设备1710可以包括，例如，微控制器(MCU)、中央处理器(CPU)、可编程逻辑器件(PLD)、专用集成电路(ASIC)、单片微型计算机(SCM)、系统芯片(SoC)等。在一些实施例中，控制设备1710可以是工控机。The control device 1710 can be used to control one or more devices or components of the medical treatment device 1700 and perform corresponding operations. The control device 1710 can generate corresponding instructions based on the device or component being controlled and the operations that need to be performed. The instructions are conveyed to the corresponding device or component in the form of electrical signals, causing the device or component to perform corresponding operations. The control device 1710 may include, for example, a microcontroller (MCU), a central processing unit (CPU), a programmable logic device (PLD), an application specific integrated circuit (ASIC), a single chip microcomputer (SCM), a system on a chip ( SoC) etc. In some embodiments, the control device 1710 may be an industrial computer.
在一些实施例中，控制设备1710集成有OCT控制模块1711、LITT控制模块1713、FBG控制模块1715、探针传感模块1717以及驱动控制模块1719。OCT控制模块1711用于控制对所述目标对象进行OCT成像。OCT控制模块1711可以通过生成指令，以控制OCT设备发射、接收光信号和/或设置成像的参数(例如，光信号带宽、光信号的中央波长、成像时间、图像对比度等)。例如，OCT控制模块1711可以通过控制OCT设备发射超过160nm带宽840nm中央波长，以及超过100nm扫频范围1300nm中央波长的双模OCT光信号。所述光信号传输至光纤滑环装置1722，在光纤滑环装置1722上进行运动控制和空间耦合处理后，最终传输至OCT探针。在一些实施例中，当LITT光子消融探针1742对目标对象进行消融时，OCT控制模块1711还可以获取生成的病理诊断信号(例如，携带组织病理特征的光信号)，以生成OCT图像。In some embodiments, the control device 1710 integrates an OCT control module 1711, a LITT control module 1713, an FBG control module 1715, a probe sensing module 1717, and a drive control module 1719. The OCT control module 1711 is used to control OCT imaging of the target object. The OCT control module 1711 can generate instructions to control the OCT device to emit and receive optical signals and/or set imaging parameters (eg, optical signal bandwidth, central wavelength of the optical signal, imaging time, image contrast, etc.). For example, the OCT control module 1711 can control the OCT device to emit a dual-mode OCT optical signal with a central wavelength of 840 nm exceeding a bandwidth of 160 nm, and a central wavelength of 1300 nm exceeding a 100 nm sweep range. The optical signal is transmitted to the optical fiber slip ring device 1722, and after motion control and spatial coupling processing is performed on the optical fiber slip ring device 1722, it is finally transmitted to the OCT probe. In some embodiments, when the LITT photon ablation probe 1742 ablates the target object, the OCT control module 1711 may also acquire the generated pathological diagnosis signal (eg, an optical signal carrying tissue pathological characteristics) to generate an OCT image.
LITT控制模块1713可以控制LITT光子消融探针1742对目标对象进行消融治疗。在一些实施例中，LITT控制模块1713集成有激光器控制器。激光器控制器可以控制LITT设备的激光器(例如，所述可调谐激光二极管和/或不可调谐激光二极管)发射激光，为整个LITT提供消融能量源。LITT控制模块1713可以控制激光器发射激光，发出的激光经光路中继处理装置1724，传输至LITT光子消融探针1742。The LITT control module 1713 can control the LITT photon ablation probe 1742 to perform ablation treatment on the target object. In some embodiments, LITT control module 1713 integrates a laser controller. The laser controller can control the laser of the LITT device (eg, the tunable laser diode and/or the non-tunable laser diode) to emit laser light to provide an ablation energy source for the entire LITT. The LITT control module 1713 can control the laser to emit laser, and the emitted laser is transmitted to the LITT photon ablation probe 1742 through the optical path relay processing device 1724.
示例性地，LITT控制模块1713控制LITT设备的激光器以特定功率(例如，以1-8W范围内选定的功率)发射特定波长(例如，980nm或1064nm)激光，该激光传输至光路中继处理装置1724进行光路中继物理连接，并进而传输给LITT光子消融探针1742，LITT光子消融探针1742发出消融激光对目标肿瘤组织进行消融。Exemplarily, the LITT control module 1713 controls the laser of the LITT device to emit laser light of a specific wavelength (e.g., 980 nm or 1064 nm) with a specific power (e.g., at a power selected in the range of 1-8W), and the laser is transmitted to the optical path relay processing The device 1724 performs a physical connection of the light path relay, and then transmits it to the LITT photon ablation probe 1742, which emits an ablation laser to ablate the target tumor tissue.
FBG控制模块1715可以控制所述测温元件获取所述目标对象边缘上特定位置的温度。测温元件的测温信号(如LITT光子测温探针1744的热源光学信号)，可以通过光路中继处理装置1724传输。在一些实施例中，FBG控制模块1715可以控制LITT光子测温探针1744实时检测所述目标对象边缘上特定位置处(例如，肿瘤组织最远边缘处，所述最远边缘是以LITT光子消融探针1742为几何测距点)的温度，并将该温度传输至光路中继处理装置1724，最终传输至FBG控制模块1715。光路中继处理装置1724支持并保障光路环形输出，避免携带温度信息的测温输出光路与测温入射光路冲突。FBG控制模块1715可以将携带温度尺度对标的光谱信号进行调制，并把光谱信号转化为电信号形式的具体温度。The FBG control module 1715 can control the temperature measuring element to obtain the temperature of a specific position on the edge of the target object. The temperature measurement signal of the temperature measurement element (such as the heat source optical signal of the LITT photon temperature measurement probe 1744) can be transmitted through the optical path relay processing device 1724. In some embodiments, the FBG control module 1715 can control the LITT photon temperature probe 1744 to detect in real time a specific position on the edge of the target object (for example, the farthest edge of the tumor tissue, the farthest edge is ablated with LITT photons). The probe 1742 is the temperature of the geometric distance measuring point, and transmits the temperature to the optical path relay processing device 1724, and finally to the FBG control module 1715. The optical path relay processing device 1724 supports and ensures the optical path ring output to avoid conflict between the temperature measurement output optical path carrying temperature information and the temperature measurement incident optical path. The FBG control module 1715 can modulate the spectral signal carrying the temperature scale benchmark, and convert the spectral signal into a specific temperature in the form of an electrical signal.
探针传感模块1717可以通过控制位移控制器1726，实时检测LITT光子消融探针1742和/或LITT光子测温探针1744的实时位置。例如，探针传感模块1717可以通过发出电信号来触发遍历位移控制器1726的位置信号反馈变化，而位移控制器1726会，例如，通过位移传感器，实时监测并与双轴立体框架1736和单轴立体框架1738交互，来实时获取LITT光子消融探针1742和LITT光子测温探针1744在患者特定部位(例如，颅内或人体其他脏器内)的位置信息。探针传感模块1717也可以实时发送控制信号给位移控制器1726，下达位移触发指令并接受位置反馈处理信号。所述位移触发指令用于触发位移控制器1726控制LITT光子消融探针1742和/或LITT光子测温探针1744运动。所述位置反馈处理信号用于基于LITT光子消融探针1742和/或LITT光子测温探针1744的实时位置，判断并决策LITT光子消融探针1742和/或LITT光子测温探针1744后续的运动(例如，继续前进、调整方向、回撤等)。The probe sensing module 1717 can detect the real-time position of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 in real time by controlling the displacement controller 1726. For example, the probe sensing module 1717 may trigger changes in position signal feedback across the ergodic displacement controller 1726 by emitting an electrical signal, and the displacement controller 1726 may monitor and communicate with the dual-axis three-dimensional frame 1736 and the single-axis stereoscopic frame 1736 in real time, for example, through a displacement sensor. The axis three-dimensional frame 1738 interacts to obtain the position information of the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 in a specific part of the patient (for example, within the skull or other organs of the human body) in real time. The probe sensing module 1717 can also send control signals to the displacement controller 1726 in real time, issue displacement triggering instructions and receive position feedback processing signals. The displacement triggering instruction is used to trigger the displacement controller 1726 to control the movement of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744. The position feedback processing signal is used to determine and decide on the subsequent positions of the LITT photon ablation probe 1742 and/or the LITT photon temperature probe 1744 based on the real-time positions of the LITT photon ablation probe 1742 and/or the LITT photon temperature probe 1744. Movement (e.g., moving forward, adjusting direction, retracing, etc.).
在一些实施例中，双轴立体框架1736和单轴立体框架1738上分别搭载有至少一个位移传感器。双轴立体框架1736上的至少一个位移传感器用于监测所述LITT光子消融探针1742的运动。单轴立体框架1738上的至少一个位移传感器用于监测所述LITT光子测温探针1744的运动。所述位移传感器可以为，例如，压电传感器、电感式传感器、涡流传感器等。In some embodiments, at least one displacement sensor is mounted on the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 respectively. At least one displacement sensor on the biaxial three-dimensional frame 1736 is used to monitor the movement of the LITT photon ablation probe 1742. At least one displacement sensor on the uniaxial three-dimensional frame 1738 is used to monitor the movement of the LITT photon temperature probe 1744. The displacement sensor may be, for example, a piezoelectric sensor, an inductive sensor, an eddy current sensor, etc.
驱动控制模块1719可以通过电信号发送指令控制驱动组件1730中第一驱动装置1732和/或第二驱动装置1734，驱动LITT光子消融探针1742和/或LITT光子测温探针1744运动。第一驱动装置1732又称为消融端驱动装置，连接并驱动LITT光子消融探针1742运动(例如，平移、旋转运动)，实现LITT光子消融探针1742两个自由度的精确运动控制。第二驱动装置1734又称为测温端驱动装置，连接并驱动LITT光子测温探针1744运动(例如，平移运动)，实现LITT光子测温探针1744一个自由度的精确运动控制。而LITT光子消融探针1742和LITT光子测温探针1744的运动实现，需要分别由双轴立体框架1736和单轴立体框架1738提供机械夹持及动力传输支持，其中，双轴提供两个不同自由度的动力传输，单轴提供单个自由度的动力传输。The drive control module 1719 can send instructions through electrical signals to control the first drive device 1732 and/or the second drive device 1734 in the drive assembly 1730 to drive the movement of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744. The first driving device 1732, also known as the ablation end driving device, is connected to and drives the LITT photon ablation probe 1742 to move (for example, translational, rotational motion) to achieve precise motion control of the LITT photon ablation probe 1742 with two degrees of freedom. The second driving device 1734 is also called the temperature measurement end driving device, which is connected to and drives the movement (for example, translational movement) of the LITT photon temperature measurement probe 1744 to realize precise motion control of the LITT photon temperature measurement probe 1744 with one degree of freedom. The movement of the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 requires mechanical clamping and power transmission support provided by the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 respectively. Among them, the biaxial three-dimensional frame 1738 provides two different Power transmission with a single degree of freedom. A single axis provides power transmission with a single degree of freedom.
接口平台集线控制模组1720集成了医学治疗装置1700的一个或多个部件或元件的中段或中继控制。示例性地，接口平台集线控制模组1720集成了上述光纤滑环装置1722、光路中继处理装置1724以及位移控制器1726。在一些实施例中，接口平台集线控制模组1720包括封装盒。光纤滑环装置1722、光路中继处理装置1724以及位移控制器1726设置于封装盒中并通过各自对应的通道连接至相应的部件或元件。例如，光纤滑环装置1722通过OCT探针通道(光纤)连接至OCT探针；光路中继处理装置1724通过LITT消融探针通道和LITT测温探针通道分别连接至LITT探针和LITT光子测温探针1744；位移控制器1726通过位移传感器线缆通道连接至位移传感器。The interface platform hub control module 1720 integrates mid-level or relay control of one or more components or elements of the medical treatment device 1700 . For example, the interface platform line control module 1720 integrates the above-mentioned optical fiber slip ring device 1722, optical path relay processing device 1724 and displacement controller 1726. In some embodiments, the interface platform hub control module 1720 includes a packaging box. The optical fiber slip ring device 1722, the optical path relay processing device 1724, and the displacement controller 1726 are provided in the packaging box and connected to corresponding components or components through respective corresponding channels. For example, the optical fiber slip ring device 1722 is connected to the OCT probe through the OCT probe channel (optical fiber); the optical path relay processing device 1724 is connected to the LITT probe and the LITT photon measurement probe through the LITT ablation probe channel and the LITT temperature measurement probe channel respectively. Temperature probe 1744; displacement controller 1726 is connected to the displacement sensor through a displacement sensor cable channel.
光纤滑环装置1722可以设置于OCT设备产生的光信号的传播路径(例如，旋转接头处)上。通过采用光纤滑环装置，以保证光信号的不间断传输。对于双模OCT，可以采用多通道光纤滑环装置(如双通道光纤滑环装置，以适配上述两种不同中央波长的光信号)，也称为多模光纤滑环装置。The optical fiber slip ring device 1722 may be disposed on the propagation path of the optical signal generated by the OCT device (for example, at the rotary joint). The optical fiber slip ring device is used to ensure uninterrupted transmission of optical signals. For dual-mode OCT, a multi-channel optical fiber slip ring device can be used (such as a dual-channel optical fiber slip ring device to adapt to the above-mentioned two optical signals with different central wavelengths), also called a multi-mode optical fiber slip ring device.
光路中继处理装置1724用于对光信号进行处理并保证光信号传播的连续性。在一些实施例中，LITT设备的激光器发出的激光经光路中继处理装置1724处理后，传输至LITT探针。所述光路中继处理装置1724可以对所述激光的至少一个参数(例如，功率、频率等)进行调整。例如，所述光路中继处理装置1724可以补偿激光的衰减，使其达到特定的功率，或对激光进行衰减处理，使其功率满足治疗的需要。在一些实施例中，光路中继处理装置1724支持并保障测温设备的光路相向传输，避免携带温度信息的测温输出光路与测温入射光路冲突，从而使光信号中断或相互干扰。The optical path relay processing device 1724 is used to process optical signals and ensure the continuity of optical signal propagation. In some embodiments, the laser light emitted by the laser of the LITT device is processed by the optical path relay processing device 1724 and then transmitted to the LITT probe. The optical path relay processing device 1724 can adjust at least one parameter (eg, power, frequency, etc.) of the laser. For example, the optical path relay processing device 1724 can compensate for the attenuation of the laser so that it reaches a specific power, or perform attenuation processing on the laser so that its power meets the needs of treatment. In some embodiments, the optical path relay processing device 1724 supports and ensures the opposite transmission of the optical paths of the temperature measurement equipment to avoid the conflict between the temperature measurement output optical path carrying temperature information and the temperature measurement incident optical path, thereby interrupting or interfering with each other in optical signals.
位移控制器1726可以基于探针传感模块1717的指令，控制LITT光子消融探针1742和/或LITT光子测温探针1744的位移。在对目标对象治疗时，位移控制器1726可以控制LITT光子消融探针1742经由双轴立体框架1736上设置的LITT消融探针通道，穿过患者特定部位(例如，穿过头骨，进入其颅内)，根据LITT光子消融探针1742的入针规划和入针指引，到达所述目标对象所在位置。同时，位移控制器1726可以控制LITT光子测温探针1744经由单轴立体框架1738上固定设置的LITT测温探针通道，穿过患者特定部位(例如，穿过头骨，进入其颅内)，根据LITT光子测温探针1744的入针规划和入针指引，到达所述目标对象所在位置，以对位于LITT光子测温探针1744特定距离处的目标对象边缘或周围组织)进行测温。其中，双轴立体框架1736和单轴立体框架1738固定到患者特定部位(例如，头部、胸腔、四肢等)的相近位置处。The displacement controller 1726 may control the displacement of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 based on instructions from the probe sensing module 1717 . When treating the target object, the displacement controller 1726 can control the LITT photon ablation probe 1742 to pass through a specific part of the patient (for example, through the skull and into the skull) through the LITT ablation probe channel provided on the biaxial stereoscopic frame 1736 ), according to the needle insertion planning and needle insertion guidance of the LITT photon ablation probe 1742, the location of the target object is reached. At the same time, the displacement controller 1726 can control the LITT photon temperature measurement probe 1744 to pass through a specific part of the patient (for example, through the skull and into the skull) through the LITT temperature measurement probe channel fixedly provided on the single-axis three-dimensional frame 1738. According to the needle insertion plan and needle insertion guide of the LITT photon temperature measurement probe 1744, the location of the target object is reached to measure the temperature of the edge of the target object or surrounding tissue located at a specific distance from the LITT photon temperature measurement probe 1744. Among them, the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 are fixed to similar positions on specific parts of the patient (eg, head, chest, limbs, etc.).
驱动组件1730用于驱动LITT光子消融探针1742和/或LITT光子测温探针1744运动，使所述LITT光子消融探针1742和/或LITT光子测温探针1744到达或远离特定位置(例如，所述目标对象所在位置)。所述LITT光子消融探针1742的运动可以包括平移运动和旋转运动。所述LITT光子测温探针1744的运动可以包括平移运动。在一些实施例中，驱动组件1730包括第一驱动装置1732(又称消融端驱动装置)和第二驱动装置1734(又称测温端驱动装置)，分别控制所述LITT光子消融探针1742和所述LITT光子测温探针1744运动。所述第一驱动装置1732与所述第二驱动装置1734独立。每个驱动装置均可包括驱动马达、线缆以及运动控制机构。所述LITT光子消融探针1742和所述LITT光子测温探针1744通过各自连接的线缆，分别物理连接于对应的运动控制机构。通过各自对应的线缆和运动控制机构，可以将对应的驱动马达输出的力分别传递至所述LITT光子消融探针1742和所述LITT光子测温探针1744，以控制其运动。The driving component 1730 is used to drive the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 to move, so that the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 reaches or moves away from a specific position (for example, , the location of the target object). The movement of the LITT photon ablation probe 1742 may include translational movement and rotational movement. The movement of the LITT photon thermometer probe 1744 may include translational movement. In some embodiments, the driving assembly 1730 includes a first driving device 1732 (also called an ablation end driving device) and a second driving device 1734 (also called a temperature measurement end driving device), which respectively control the LITT photon ablation probe 1742 and The LITT photon thermometer probe 1744 moves. The first driving device 1732 is independent of the second driving device 1734 . Each drive device may include a drive motor, cables, and motion control mechanisms. The LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 are physically connected to corresponding motion control mechanisms through respective connected cables. Through corresponding cables and motion control mechanisms, the force output by the corresponding drive motor can be transmitted to the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 to control their movement.
在本实施例中，所述第一驱动装置1732耦合于所述LITT光子消融探针1742，并控制所述LITT光子消融探针1742的平移运动和旋转运动。所述第一驱动装置234包括第一驱动马达、第一平移线缆、第一平移控制机构 和第一旋转线缆、第一旋转控制机构。所述第一平移控制机构用于控制所述LITT光子消融探针1742的平移运动。所述第一旋转控制机构用于控制所述LITT光子消融探针1742的旋转运动。所述第一平移线缆和第一旋转线缆分别连接于所述第一平移控制机构和第一旋转控制机构，所述第一平移控制机构和第一旋转控制机构连接于所述LITT光子消融探针1742，通过所述第一平移线缆和所述第一旋转线缆，分别控制所述LITT光子消融探针1742的平移运动和旋转运动。所述第一驱动马达可以根据需求，带动第一平移线缆和/或第一旋转线缆运动，从而控制所述LITT光子消融探针1742的平移和/或旋转运动，实现所述LITT光子消融探针1742两个自由度的精确运动控制。在一些实施例中，所述第一平移控制机构和第一旋转控制机构可以设置于双轴立体框架1736。In this embodiment, the first driving device 1732 is coupled to the LITT photon ablation probe 1742 and controls the translational movement and rotational movement of the LITT photon ablation probe 1742. The first driving device 234 includes a first driving motor, a first translation cable, a first translation control mechanism, a first rotation cable, and a first rotation control mechanism. The first translation control mechanism is used to control the translation movement of the LITT photon ablation probe 1742. The first rotation control mechanism is used to control the rotation movement of the LITT photon ablation probe 1742. The first translation cable and the first rotation cable are respectively connected to the first translation control mechanism and the first rotation control mechanism, and the first translation control mechanism and the first rotation control mechanism are connected to the LITT photon ablation The probe 1742 controls the translational movement and rotational movement of the LITT photon ablation probe 1742 through the first translation cable and the first rotation cable respectively. The first drive motor can drive the movement of the first translation cable and/or the first rotation cable as required, thereby controlling the translation and/or rotation movement of the LITT photon ablation probe 1742 to achieve the LITT photon ablation. Precise motion control of probe 1742 with two degrees of freedom. In some embodiments, the first translation control mechanism and the first rotation control mechanism may be provided on the biaxial three-dimensional frame 1736 .
所述第二驱动装置1734耦合于所述LITT光子测温探针1744，并控制所述LITT光子测温探针1744的平移运动。所述第二驱动装置1734包括第二驱动马达、第二平移线缆和第二平移控制机构。所述第二平移控制机构用于控制所述LITT光子测温探针1744的平移运动。所述第二平移线缆连接于所述第二平移控制机构，所述第二平移控制机构连接于所述LITT光子测温探针1744，通过所述第二平移线缆控制所述LITT光子测温探针1744的平移运动。所述第二驱动马达可以根据需求，带动第二平移线缆运动，从而控制所述LITT光子测温探针1744平移运动，实现所述LITT光子测温探针1744一个自由度的精确运动控制。在一些实施例中，所述第二平移控制机构可以设置于单轴立体框架1738。The second driving device 1734 is coupled to the LITT photon temperature measurement probe 1744 and controls the translational movement of the LITT photon temperature measurement probe 1744. The second driving device 1734 includes a second driving motor, a second translation cable, and a second translation control mechanism. The second translation control mechanism is used to control the translation movement of the LITT photon temperature measurement probe 1744. The second translation cable is connected to the second translation control mechanism, the second translation control mechanism is connected to the LITT photon temperature measurement probe 1744, and the LITT photon temperature measurement probe is controlled through the second translation cable. Translational movement of temperature probe 1744. The second drive motor can drive the movement of the second translation cable as required, thereby controlling the translational movement of the LITT photon temperature measurement probe 1744 and achieving precise motion control of one degree of freedom of the LITT photon temperature measurement probe 1744 . In some embodiments, the second translation control mechanism may be provided on the single-axis three-dimensional frame 1738.
在一些实施例中，上述线缆(如第一平移线缆、第一旋转线缆、第二平移线缆)为特制丝线，具有较高刚性、较低的弹性模量，可实时1:1完成扭矩传输，以确保驱动所述LITT光子消融探针1742和/或LITT光子测温探针1744运动的准确性。In some embodiments, the above-mentioned cables (such as the first translation cable, the first rotation cable, and the second translation cable) are special silk threads with higher rigidity and lower elastic modulus, and can complete torque transmission in real time 1:1 to ensure the accuracy of driving the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 to move.
双轴立体框架1736和单轴立体框架1738可以搭载医学治疗装置1700的一个或多个部件或元件。示例性地，所述双轴立体框架1736搭载的部件或元件包括LITT光子消融探针1742的LITT消融探针通道，位移传感器，第一运动控制机构(如所述第一平移控制机构和第一旋转控制机构)等。所述单轴立体框架1738搭载的部件或元件包括LITT光子测温探针1744的LITT测温探针通道，位移传感器，第二平移控制机构等。所述双轴立体框架1736和单轴立体框架1738可以固定到患者特定部位(例如，颅骨的两处不同位置)，与患者特定部位保持稳定连接，不发生相对位移。双轴立体框架1736和单轴立体框架1738搭载的部件或元件可以分别固定连接至所述双轴立体框架1736和单轴立体框架1738。Biaxial stereoscopic frame 1736 and uniaxial stereoscopic frame 1738 may carry one or more components or elements of medical treatment device 1700 . Exemplarily, the components or elements carried by the biaxial three-dimensional frame 1736 include the LITT ablation probe channel of the LITT photon ablation probe 1742, a displacement sensor, a first motion control mechanism (such as the first translation control mechanism and the first Rotation control mechanism), etc. The components or elements carried by the single-axis three-dimensional frame 1738 include the LITT temperature measurement probe channel of the LITT photon temperature measurement probe 1744, a displacement sensor, a second translation control mechanism, etc. The biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 can be fixed to a specific part of the patient (for example, two different positions of the skull), and maintain a stable connection with the specific part of the patient without relative displacement. The components or elements carried by the biaxial three-dimensional frame 1736 and the single-axial three-dimensional frame 1738 can be fixedly connected to the biaxial three-dimensional frame 1736 and the single-axial three-dimensional frame 1738, respectively.
温度反馈控制单元1750用于监测LITT光子测温探针1744测得的目标对象边缘上特定位置处的温度，并确保测得的温度处于预设温度范围内。所述预设温度范围由用户设定，根据系统默认设置等。例如，所述预设温度范围为44±0.5℃，44±1℃，45±0.5℃，45±1℃，46±0.5℃，46±1℃，47±0.5℃，47±1℃，48±0.5℃，48±1℃等。在一些实施例中，所述预设温度范围为46±1℃。目标对象的组织温度处于此预设温度范围下具有更好的治疗效果。此时，医学治疗装置1700工作时的治疗效果最好，治疗的成功率和治疗效率最高。温度反馈控制单元1750连接于FBG控制模块1715。FBG控制模块1715可以将LITT光子测温探针1744测得的温度以电信号传输至温度反馈控制单元1750。所述测得的温度的传输可以是实时性的或间歇性的(例如，周期性的)。在一些实施例中，当所述LITT光子测温探针1744测得的温度超出预设温度范围时，温度反馈控制单元1750可以确定测得的温度与所述预设温度范围的差值(即温度差)，并将所述差值输出至激光剂量控制单元1760以调整LITT光子消融探针1742输出的激光剂量，从而使LITT光子测温探针1744测得的温度回到所述预设温度范围内。The temperature feedback control unit 1750 is used to monitor the temperature at a specific position on the edge of the target object measured by the LITT photon temperature probe 1744, and ensure that the measured temperature is within a preset temperature range. The preset temperature range is set by the user, based on system default settings, etc. For example, the preset temperature range is 44±0.5℃, 44±1℃, 45±0.5℃, 45±1℃, 46±0.5℃, 46±1℃, 47±0.5℃, 47±1℃, 48 ±0.5℃, 48±1℃, etc. In some embodiments, the preset temperature range is 46±1°C. The target object's tissue temperature is within this preset temperature range for better therapeutic effects. At this time, the medical treatment device 1700 has the best therapeutic effect when working, and the treatment success rate and treatment efficiency are the highest. The temperature feedback control unit 1750 is connected to the FBG control module 1715. The FBG control module 1715 may transmit the temperature measured by the LITT photon temperature probe 1744 to the temperature feedback control unit 1750 as an electrical signal. The transmission of the measured temperature may be real-time or intermittent (eg, periodic). In some embodiments, when the temperature measured by the LITT photon temperature probe 1744 exceeds the preset temperature range, the temperature feedback control unit 1750 may determine the difference between the measured temperature and the preset temperature range (i.e. temperature difference), and output the difference value to the laser dose control unit 1760 to adjust the laser dose output by the LITT photon ablation probe 1742, so that the temperature measured by the LITT photon temperature measurement probe 1744 returns to the preset temperature within the range.
激光剂量控制单元1760可以确定目标激光输出剂量值(即需要输出的目标激光剂量值。激光剂量控制单元1760可以连接于温度反馈控制单元1750。激光剂量控制单元1760可以获取温度反馈控制单元1750确定的温度差，并基于所述温度差，确定所述目标激光输出剂量值。所述目标激光输出剂量值可以是某个特定时间段内激光的总剂量，也可以是各个时刻下激光的剂量值。通过所述时间段内激光的总剂量或各个时刻激光的剂量值，可以确定LITT光子测温探针1744处组织温度的变化趋势，以使得LITT光子测温探针1744测得的温度重新回到所述预设温度范围内。The laser dose control unit 1760 can determine the target laser output dose value (ie, the target laser dose value that needs to be output). The laser dose control unit 1760 can be connected to the temperature feedback control unit 1750. The laser dose control unit 1760 can obtain the value determined by the temperature feedback control unit 1750. temperature difference, and based on the temperature difference, the target laser output dose value is determined. The target laser output dose value can be the total dose of laser within a specific time period, or it can be the dose value of laser at each time. Through the total dose of the laser during the time period or the dose value of the laser at each moment, the changing trend of the tissue temperature at the LITT photon temperature measurement probe 1744 can be determined, so that the temperature measured by the LITT photon temperature measurement probe 1744 returns to within the preset temperature range.
在一些实施例中，上述确定LITT光子测温探针1744处组织温度的变化趋势的过程可以基于模型或者特定算法确定。所述模型可以是，例如，机器学习模型。示例性的机器学习模型可以包括神经网络模型(例如，深度学习模型)、生成对抗网络(GAN)、深度置信网络(DBN)、堆叠自动编码器(SAE)、逻辑回归(LR)模型、支持向量机(SVM)模型、决策树模型、朴素贝叶斯模型、随机森林模型或受限玻尔兹曼机(RBM)、梯度提升决策树(GBDT)模型、LambdaMART模型、自适应增强模型、隐马尔可夫模型、感知器神经网络模型、Hopfield网络模型等或其任意组合。示例性的深度学习模型可以包括深度神经网络(DNN)模型、卷积神经网络(CNN)模型、递归神经网络(RNN)模型、特征金字塔网络(FPN)模型等。示例性的CNN模型可以包括V-Net模型、U-Net模型、FB-Net模型、Link-Net模型等，或其任意组合。通过历史数据(例如，历史激光剂量与历史温度差)，可以对所述模型进行训练，以此生成训练后的模型，以确定所述目标激光输出剂量值。In some embodiments, the above process of determining the changing trend of tissue temperature at the LITT photon thermometer probe 1744 can be determined based on a model or a specific algorithm. The model may be, for example, a machine learning model. Exemplary machine learning models may include neural network models (e.g., deep learning models), generative adversarial networks (GAN), deep belief networks (DBN), stacked autoencoders (SAE), logistic regression (LR) models, support vectors Machine (SVM) model, decision tree model, naive Bayes model, random forest model or restricted Boltzmann machine (RBM), gradient boosted decision tree (GBDT) model, LambdaMART model, adaptive enhancement model, hidden Martian Kov model, perceptron neural network model, Hopfield network model, etc. or any combination thereof. Exemplary deep learning models may include deep neural network (DNN) models, convolutional neural network (CNN) models, recurrent neural network (RNN) models, feature pyramid network (FPN) models, etc. Exemplary CNN models may include V-Net models, U-Net models, FB-Net models, Link-Net models, etc., or any combination thereof. The model can be trained through historical data (for example, historical laser dose and historical temperature difference), thereby generating a trained model to determine the target laser output dose value.
衰减器调节控制单元1770可以连接并控制衰减器调节单元1780，使得激光功率衰减器1790对输出激光的功率进行调整。在一些实施例中，激光功率衰减器1790可以是SMA可变高功率激光衰减器。在一些实施例中，SMA可变高功率激光衰减器上设置有功率调整螺母。通过调节螺母的正、反向调节，可以调节输出激光的功率。衰减器调节控制单元1770可以基于当前激光输出剂量值与目标激光输出剂量值，确定调节螺母的调节方向及调节量(例如，螺母旋转的圈数)。在一些实施例中，所述温度反馈控制单元1750、激光剂量控制单元1760和/或衰减器调节控制单元1770可以整体作为处理模块，所述处理模块相对于所述控制设备1710独立运行并与医学治疗设备1700的各部件或设备相互连接。当所述测温元件测得的温度超出预设温度范围时，所述处理模块可以基于测得的温度与所述预设温度范围的差值，确定所述LITT设备的目标激光输出剂量值，使得所述测温元件测得的温度处于所述预设温度范围。所述处理模块可以是或包括，例如，微控制器(MCU)、中央处理器(CPU)、可编程逻辑器件(PLD)、专用集成电路(ASIC)、单片微型计算机(SCM)、系统芯片(SoC)等。在一些实施例中，所述温度反馈控制单元1750、激光剂量控制单元1760和/或衰减器调节控制单元1770可以集成于控制设备1710或作为控制设备1710的一部分。The attenuator adjustment control unit 1770 can be connected to and control the attenuator adjustment unit 1780 so that the laser power attenuator 1790 adjusts the power of the output laser. In some embodiments, laser power attenuator 1790 may be an SMA variable high power laser attenuator. In some embodiments, the SMA variable high-power laser attenuator is provided with a power adjustment nut. By adjusting the forward and reverse adjustment of the nut, the output laser power can be adjusted. The attenuator adjustment control unit 1770 may determine the adjustment direction and adjustment amount of the adjustment nut (for example, the number of turns of the nut) based on the current laser output dose value and the target laser output dose value. In some embodiments, the temperature feedback control unit 1750, the laser dose control unit 1760 and/or the attenuator adjustment control unit 1770 can be integrated as a processing module, and the processing module operates independently with respect to the control device 1710 and is connected with the medical device 1710. The various components or devices of treatment device 1700 are connected to each other. When the temperature measured by the temperature measuring element exceeds the preset temperature range, the processing module may determine the target laser output dose value of the LITT device based on the difference between the measured temperature and the preset temperature range, so that the temperature measured by the temperature measuring element is within the preset temperature range. The processing module may be or include, for example, a microcontroller (MCU), a central processing unit (CPU), a programmable logic device (PLD), an application specific integrated circuit (ASIC), a single chip microcomputer (SCM), a system on a chip (SoC) etc. In some embodiments, the temperature feedback control unit 1750 , the laser dose control unit 1760 and/or the attenuator adjustment control unit 1770 may be integrated into or part of the control device 1710 .
衰减器调节单元1780可以连接并控制激光功率衰减器1790。衰减器调节单元1780可以基于衰减器调节控制单元1770生成的指令(例如，上述螺母的调节方向及调节量)，控制激光功率衰减器1790对输入的激光功率进行一定比例的衰减或增益。参照上述实施例，激光功率衰减器1790为SMA可变高功率激光衰减器，此时衰减器调节单元1780可以是，例如，电动螺旋调节步进元件。所述电动螺旋调节步进元件可以包括微型驱动马达。通过所述微型驱动马达，可以根据确定的螺母的调节方向及调节量，调节所述螺母。The attenuator adjustment unit 1780 can be connected to and control the laser power attenuator 1790. The attenuator adjustment unit 1780 can control the laser power attenuator 1790 to attenuate or gain the input laser power by a certain proportion based on the instructions generated by the attenuator adjustment control unit 1770 (for example, the adjustment direction and adjustment amount of the above-mentioned nut). Referring to the above embodiment, the laser power attenuator 1790 is an SMA variable high-power laser attenuator. In this case, the attenuator adjustment unit 1780 can be, for example, an electric screw adjustment stepping element. The electric screw adjustment stepping element can include a micro drive motor. Through the micro drive motor, the nut can be adjusted according to the determined adjustment direction and adjustment amount of the nut.
激光功率衰减器1790可以通过对输入的激光功率进行一定比例的衰减或增益，将当前激光输出剂量值调整为所述目标激光输出剂量值。激光功率衰减器1790可以对输入的激光功率衰减，例如，10％，20％，30％，40％，50％，60％，70％，80％或90％，或者增益，例如，10％，20％，30％，40％，50％，60％，70％，80％，90％，100％，120％，150％等(即进行功率衰减/增益处理)。所述激光功率衰减器1790通过动态调整所述当前激光输出剂量值，使得测温元件测得的温度始终处于所述预设温度范围。The laser power attenuator 1790 can adjust the current laser output dose value to the target laser output dose value by attenuating or gaining a certain proportion of the input laser power. The laser power attenuator 1790 can attenuate the input laser power by, for example, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80% or 90%, or gain, for example, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80%, 90%, 100%, 120%, 150%, etc. (i.e. power attenuation/gain processing). The laser power attenuator 1790 dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measuring element is always within the preset temperature range.
通过上述温度反馈控制单元1750、激光剂量控制单元1760、衰减器调节控制单元1770、衰减器调节单元1780，所述激光功率衰减器1790通过动态调整所述当前激光输出剂量值，使得测温元件测得的温度始终处于所述预设温度范围，此时LITT设备的激光器输出的激光功率始终为目标激光输出剂量值，所述激光经光路中继处理装置1724，传输至LITT光子消融探针1742达到调整适配激光消融能量的目的。上述各模块、单元或元件之间的操作可以是一个动态调整过程，通过往复循环，以使得LITT光子测温探针1744测得的温度(例如，目标对象最远边缘的温度)始终动态维持在预设温度范围内。各单元之间建立了电连接，温控信号以电信号的形式实时且稳定的传递，结合LITT光子测温探针1744的准确性(相比之前MRTI测温更加准确)，由此提高了温度控制的精度以及反馈调整的及时性，使得相对于LITT光子消融探针1742的目标对象最远边缘处温度始终保持在所述预设温度范围内，由此保证了治疗的效果。Through the above-mentioned temperature feedback control unit 1750, laser dose control unit 1760, attenuator adjustment control unit 1770, and attenuator adjustment unit 1780, the laser power attenuator 1790 dynamically adjusts the current laser output dose value so that the temperature measurement element measures The obtained temperature is always within the preset temperature range. At this time, the laser power output by the laser of the LITT device is always the target laser output dose value. The laser is transmitted to the LITT photon ablation probe 1742 through the optical path relay processing device 1724 to reach Adjust and adapt the laser ablation energy to the purpose. The operation between the above-mentioned modules, units or components can be a dynamic adjustment process, through a back-and-forth cycle, so that the temperature measured by the LITT photon temperature measurement probe 1744 (for example, the temperature of the farthest edge of the target object) is always dynamically maintained at within the preset temperature range. Electrical connections are established between each unit, and the temperature control signal is transmitted in real time and stably in the form of an electrical signal. Combined with the accuracy of the LITT photon temperature measurement probe 1744 (more accurate than the previous MRTI temperature measurement), the temperature is increased. The precision of the control and the timeliness of the feedback adjustment ensure that the temperature at the farthest edge of the target object relative to the LITT photon ablation probe 1742 is always maintained within the preset temperature range, thus ensuring the treatment effect.
图18是根据本说明书一些实施例所示的LITT光子测温探针的示意图。Figure 18 is a schematic diagram of a LITT photon temperature measurement probe according to some embodiments of the present specification.
LITT光子测温探针1805设置于探针套管中，所述探针套管由耐高温、耐腐蚀的特定材料，例如，聚醚醚酮(PEEK)制成。LITT光子测温探针1805可以是FBG测温探针(又称FBG传感器)。所述FBG测温探针包括使用特殊原材料制备的光纤，其经过特定波长范围(例如，240-244nm，244-248nm，248-252nm，252-256nm等)的紫外光照射而成。示例性地，可以将制备所述FBG测温探针的原材料固定于固定器件(例如，夹具)，所述固定器件固定连接于运动驱动器。由激光器控制器控制激光器发射激光，所述激光依次经过光束校正装置(例如，两个相对设置的248nm特征波长准分子激光45°线镜)，狭缝光阑(例如，4.5mm宽度的光阑)，紫外镀膜透镜(例如，245-440nm特征波长紫外镀膜熔融石英平凸圆柱透镜)和相位掩膜(例如，紫外辐照248nm特征波长1460-1600nm超带宽相位掩膜)后，在所述原材料表面产生条带状光斑。然后由运动驱动控制器控制运动驱动器，驱动所述原材料运动，在所述原材料运动过程中，通过所述激光照射所述原材料，从而形成所述FBG测温探针。The LITT photon temperature measurement probe 1805 is arranged in a probe sleeve, which is made of a specific material that is resistant to high temperatures and corrosion, such as polyetheretherketone (PEEK). LITT photon temperature measurement probe 1805 can be an FBG temperature measurement probe (also known as FBG sensor). The FBG temperature measurement probe includes an optical fiber prepared using special raw materials, which is irradiated with ultraviolet light in a specific wavelength range (for example, 240-244nm, 244-248nm, 248-252nm, 252-256nm, etc.). For example, the raw material for preparing the FBG temperature measurement probe can be fixed on a fixing device (for example, a clamp), and the fixing device is fixedly connected to the motion driver. The laser controller controls the laser to emit laser, which passes through the beam correction device (for example, two oppositely arranged 248nm characteristic wavelength excimer laser 45° line mirrors), the slit diaphragm (for example, a 4.5mm width diaphragm) ), after UV coating lens (for example, 245-440nm characteristic wavelength UV coating fused silica plano-convex cylindrical lens) and phase mask (for example, UV irradiation 248nm characteristic wavelength 1460-1600nm ultra-bandwidth phase mask), after the raw material Strip-like spots appear on the surface. Then, the motion drive controller controls the motion driver to drive the raw material to move. During the movement of the raw material, the raw material is irradiated by the laser, thereby forming the FBG temperature measurement probe.
在治疗过程中，驱动马达1810(例如，上述第二驱动设备)可以提供驱动力，通过支持前进/回撤平移运动的驱动线缆1815(例如，上述第二平移线缆)对单轴立体框架1820(例如，上述单轴立体框架1738)提供驱动力，使LITT光子测温探针1805进行前进/回撤平移运动，从而到达目标对象边缘处的特定位置(例如，图20中所示的位置)。在此期间，位移传感器(图中未示出)，设置于单轴立体框架1820，可以监测所述LITT光子测温探针1744的运动位置。位移传感器的传感信号通过位移传感器线缆1825进行传输。LITT光子测温探针1805测得的温度传感光谱光信号，通过LITT测温探针通道1830，实时发送至温度反馈控制单元1750。集成元件1835为LITT测温探针通道1830挂载便携式连接器提供接口支持。During treatment, the drive motor 1810 (e.g., the second drive device described above) may provide driving force to the single-axis stereotaxic frame via the drive cable 1815 (e.g., the second translation cable described above) that supports forward/retract translation motion. 1820 (e.g., the single-axis three-dimensional frame 1738 described above) provides the driving force to cause the LITT photon thermometer probe 1805 to perform forward/retract translation motion to reach a specific position at the edge of the target object (e.g., the position shown in FIG. 20 ). During this period, a displacement sensor (not shown in the figure), installed on the single-axis three-dimensional frame 1820, can monitor the movement position of the LITT photon temperature measurement probe 1744. The sensing signal of the displacement sensor is transmitted through the displacement sensor cable 1825. The temperature sensing spectrum light signal measured by the LITT photon temperature measurement probe 1805 is sent to the temperature feedback control unit 1750 in real time through the LITT temperature measurement probe channel 1830. The integrated component 1835 provides interface support for the portable connector mounted on the LITT temperature measurement probe channel 1830.
图19是根据本说明书一些实施例所示的LITT光子消融探针的示意图。Figure 19 is a schematic diagram of a LITT photon ablation probe according to some embodiments of the present specification.
如图19所示，LITT光子消融探针可以为LITT光子侧向消融探针1910或LITT光子周向消融探针1920。在一些实施例中，LITT光子侧向消融探针1910可以包括OCT探针1912和LITT侧向消融探针1914。LITT光子周向消融探针1920可以包括OCT探针1922和LITT周向消融探针1924。LITT光子侧向消融探针1910和LITT光子周向消融探针1920可以各自包括一个探针套管，所述探针套管由耐高温、耐腐蚀的特定材料，例如，聚醚醚酮(PEEK)制成。As shown in Figure 19, the LITT photon ablation probe may be a LITT photon lateral ablation probe 1910 or a LITT photon circumferential ablation probe 1920. In some embodiments, LITT photon lateral ablation probe 1910 may include an OCT probe 1912 and a LITT lateral ablation probe 1914. LITT photon circumferential ablation probe 1920 may include an OCT probe 1922 and a LITT circumferential ablation probe 1924. The LITT photon lateral ablation probe 1910 and the LITT photon circumferential ablation probe 1920 may each include a probe sleeve made of a specific material that is resistant to high temperatures and corrosion, such as polyetheretherketone (PEEK). )production.
所述LITT侧向消融探针1914包括探针主体、连接面和镀层。连接面为主体与镀层之间的连接界面。探针主体呈圆柱体状。探针主体由针芯和位于针芯外周的硬质包层构成。所述针芯由纯二氧化硅材料制成。所述硬质包层由技术增强型包层二氧化硅(TECS)材料制成。在一些实施例中，探针主体的端部(远端)具有一定倾角(即探针主体的端面与探针主体的轴线呈一定夹角，所述夹角为锐角)。所述连接面为通过对所述探针主体端面进行光洁化而形成。所述镀层采用贵金属(例如，金、银和铂族金属)靶材镀层。在一些实施例中，所述镀层可以通过在连接面的表面进行磁控溅射镀膜形成。The LITT lateral ablation probe 1914 includes a probe body, a connection surface and a coating. The connection surface is the connection interface between the body and the coating. The probe body is cylindrical. The probe body consists of a needle core and a hard cladding located on the outer periphery of the needle core. The needle core is made of pure silicon dioxide material. The hard cladding is made from Technology Enhanced Cladding Silica (TECS) material. In some embodiments, the end (distal end) of the probe body has a certain inclination angle (that is, the end surface of the probe body forms a certain angle with the axis of the probe body, and the included angle is an acute angle). The connection surface is formed by smoothing the end surface of the probe body. The plating uses noble metal (eg, gold, silver, and platinum group metals) target plating. In some embodiments, the coating layer may be formed by magnetron sputtering coating on the surface of the connection surface.
在一些实施例中，LITT侧向消融探针1914的镀层可以替换为透镜(例如，蓝宝石透镜)。此时，所述探针主体的端部(远端)可以为平直表面或具有一定倾角(即探针主体的端面与探针主体的轴线垂直或呈一定夹角，所述夹角为锐角)。所述连接面与透镜之间，通过电弧焊接或钨(如钨丝)、铱(如铱丝)等材料的高温熔融而熔接，并在钨或铱的高温熔融熔接选择下行钨丝或铱丝下火抛光工艺，即对熔接面进行火抛光。In some embodiments, the coating of the LITT lateral ablation probe 1914 may be replaced with a lens (eg, a sapphire lens). At this time, the end (distal end) of the probe body can be a straight surface or have a certain inclination angle (that is, the end surface of the probe body is perpendicular to or at a certain angle with the axis of the probe body, and the included angle is an acute angle) ). The connection surface and the lens are welded by arc welding or high-temperature melting of tungsten (such as tungsten wire), iridium (such as iridium wire) and other materials, and the tungsten wire or iridium wire is selected for the high-temperature melting of tungsten or iridium. The fire polishing process is to fire polish the welded surface.
所述LITT周向消融探针1924可以包括探针主体。探针主体由针芯和位于针芯外周的硬质包层构成。所述针芯由纯二氧化硅材料制成。所述硬质包层由技术增强型包层二氧化硅(TECS)材料制成。探针主体的远端(靠近目标对象的端部)，设置锥形面。所述锥形面的直径由初始直径逐渐缩小至预设直径。所述锥形面上设置有凹槽，例如，通过光机雕刻形成。传导至LITT周向消融探针的激光可以从所述凹槽中出射。所述凹槽呈一定花纹状(例如，螺纹状)沿锥形面均匀(弥散)分布，并且互相不重叠。所述凹槽的分布花纹为单螺纹形状(螺旋状)、多螺纹交叉形状(例如，双螺纹交叉)、菱形网格形状、蜂窝形状等，或其组合。在本实施例中，LITT侧向消融探针1914和LITT周向消融探针1924分别与图6-11中所述的LITT侧向消融探针700、800和LITT周向消融探针900相同或相似，此处不再赘述。The LITT circumferential ablation probe 1924 may include a probe body. The probe body consists of a needle core and a hard cladding located on the outer periphery of the needle core. The needle core is made of pure silicon dioxide material. The hard cladding is made from Technology Enhanced Cladding Silica (TECS) material. At the far end of the probe body (the end closest to the target object), a tapered surface is set. The diameter of the tapered surface gradually decreases from the initial diameter to the preset diameter. The tapered surface is provided with grooves, for example, formed by optical machine engraving. Laser light directed to the LITT circumferential ablation probe can emerge from the groove. The grooves are evenly (dispersed) distributed along the tapered surface in a certain pattern shape (for example, thread shape) and do not overlap with each other. The distribution pattern of the grooves is a single thread shape (spiral shape), a multi-thread cross shape (for example, a double thread cross), a rhombus grid shape, a honeycomb shape, etc., or a combination thereof. In this embodiment, LITT lateral ablation probe 1914 and LITT circumferential ablation probe 1924 are the same as or respectively the LITT lateral ablation probes 700, 800 and LITT circumferential ablation probe 900 described in Figures 6-11. Similar, will not be repeated here.
在治疗过程中，驱动马达1930(例如，上述第一驱动设备)可以提供驱动力，通过支持前进/回撤平移运动的驱动线缆1935(例如，上述第一平移线缆)以及支持旋转运动的驱动线缆1940(例如，上述第一旋转线缆)对双轴立体框架1945(例如，上述双轴立体框架1736)提供驱动力，使LITT光子消融探针(如LITT光子侧向消融探针1910或LITT光子周向消融探针1920)进行平移、旋转两个自由度的运动，从而到达目标对象的特定位置(例如，图20中所示的位置)，并对所述目标对象进行LITT辐照。在此期间，设置于双轴立体框架1945的位移传感器(图中未示出)可以监测所述LITT光子消融探针的运动位置。位移传感器的传感信号通过位移传感器线缆通道1950进行传输。During treatment, a drive motor 1930 (e.g., the first drive device described above) may provide drive force via a drive cable 1935 (e.g., the first translation cable described above) that supports forward/retract translational motion, and a drive cable 1935 that supports rotational motion. The driving cable 1940 (for example, the above-mentioned first rotation cable) provides driving force to the biaxial stereoscopic frame 1945 (for example, the above-mentioned biaxial stereoscopic frame 1736), so that the LITT photon ablation probe (such as the LITT photon lateral ablation probe 1910 or LITT photon circumferential ablation probe 1920) to perform translational and rotational two-degree-of-freedom movements, thereby reaching a specific position of the target object (for example, the position shown in FIG. 20), and performing LITT irradiation on the target object. . During this period, a displacement sensor (not shown in the figure) provided on the biaxial three-dimensional frame 1945 can monitor the movement position of the LITT photon ablation probe. The sensing signal of the displacement sensor is transmitted through the displacement sensor cable channel 1950.
当采用LITT光子侧向消融探针1910时，LITT侧向消融探针1914可以接收LITT消融探针通道1955传输的特定功率(例如，1-50W，1-20W，1-10W，1-8W)的高功率消融激光，通过将LITT光子侧向消融探针1910放置于所述目标对象外侧，以一定方向射向所述目标对象。同时，LITT光子侧向消融探针1910中的OCT探针1912可以实时对目标对象的消融情况或病理诊断进行扫描并成像，并实时通过OCT探针通道1960实时回传至OCT控制模块1711。所述OCT探针通道1960与所述LITT消融探针通道1955通过集成元件1965进行集成(例如，机械耦合)。When the LITT photon lateral ablation probe 1910 is used, the LITT lateral ablation probe 1914 can receive the specific power transmitted by the LITT ablation probe channel 1955 (eg, 1-50W, 1-20W, 1-10W, 1-8W) The high-power ablation laser is placed on the outside of the target object by placing the LITT photon lateral ablation probe 1910 and shoots towards the target object in a certain direction. At the same time, the OCT probe 1912 in the LITT photon lateral ablation probe 1910 can scan and image the ablation status or pathological diagnosis of the target object in real time, and transmit it back to the OCT control module 1711 through the OCT probe channel 1960 in real time. The OCT probe channel 1960 and the LITT ablation probe channel 1955 are integrated (eg, mechanically coupled) through an integration component 1965 .
当采用LITT光子周向消融探针1920时，LITT周向消融探针1924可以接收LITT消融探针通道1955传输的特定功率(例如，1-50W，1-20W，1-10W，1-8W)的高功率消融激光，并经过LITT周向消融探针1924上的凹槽弥散四周射向所述目标对象(例如，癌化组织)。同时，LITT光子周向消融探针1920中的OCT探针1922可以实时对目标对象的消融情况或病理诊断进行扫描并成像，并实时通过OCT探针通道1960实时回传至OCT控制模块1711。When the LITT photon circumferential ablation probe 1920 is used, the LITT circumferential ablation probe 1924 can receive the specific power transmitted by the LITT ablation probe channel 1955 (eg, 1-50W, 1-20W, 1-10W, 1-8W) The high-power ablation laser is diffused through the groove on the LITT circumferential ablation probe 1924 and directed towards the target object (for example, cancerous tissue). At the same time, the OCT probe 1922 in the LITT photon circumferential ablation probe 1920 can scan and image the ablation status or pathological diagnosis of the target object in real time, and transmit it back to the OCT control module 1711 through the OCT probe channel 1960 in real time.
图20是根据本说明书一些实施例所示的治疗时LITT光子消融探针及LITT光子测温探针的示意图。Figure 20 is a schematic diagram of a LITT photon ablation probe and a LITT photon temperature measurement probe during treatment according to some embodiments of this specification.
在本实施例中，在LITT光子治疗之前，可以将LITT光子测温探针2010和LITT光子消融探针(LITT光子周向消融探针2020或LITT光子侧向消融探针2030)置于预设位置。LITT光子测温探针2010可以获取所述目标对象边缘上特定位置的温度。所述特定位置可以是所述目标对象边缘上距离所述LITT光子消融探针最远的位置。所述LITT光子测温探针2010与LITT光子消融探针的距离小于所述目标对象的尺寸。所述目标对象的边缘以内的区域可以为，例如，不规则形状。所述目标对象可以被等效为圆形。例如，可以确定所述目标对象的最小外接圆，以作为所述目标对象的等效圆。所述目标对象的尺寸即为，例如，所述等效圆的直径。In this embodiment, before LITT photon treatment, the LITT photon temperature measurement probe 2010 and the LITT photon ablation probe (LITT photon circumferential ablation probe 2020 or LITT photon lateral ablation probe 2030) can be placed in a preset Location. The LITT photon temperature probe 2010 can obtain the temperature at a specific location on the edge of the target object. The specific location may be the location furthest from the LITT photon ablation probe on the edge of the target object. The distance between the LITT photon temperature measurement probe 2010 and the LITT photon ablation probe is smaller than the size of the target object. The area within the edge of the target object may be, for example, irregularly shaped. The target object may be equivalent to a circle. For example, the smallest circumscribed circle of the target object may be determined as the equivalent circle of the target object. The size of the target object is, for example, the diameter of the equivalent circle.
示例性地，如图所示，当所述LITT光子消融探针为LITT光子周向消融探针2020时，所述LITT光子周向消融探针2020(包括LITT周向消融探针)设置于所述目标对象的等效中心(即等效圆的圆心)，所述LITT光子测温探针2010设置于所述目标对象边缘上距离所述LITT光子周向消融探针2020最远处的位置。所述LITT光子周向消融探针2020与所述LITT光子测温探针2010的距离设为L 弥散。L 弥散等于或接近所述目标对象的等效半径。此处所述等效半径为所述目标对象边缘的最小外接圆的半径。结合LITT光子周向消融探针2020消融激光的(周向)弥散均匀性，通过将LITT光子周向消融探针2020设置于等效中心，而LITT光子测温探针2010设置于所述目标对象边缘上距离所述LITT光子周向消融探针2020最远处的位置，因此保证整个目标对象所在范围内的温度均高于预设温度范围，由此保证了测温的准确性，且温度从所述等效中心向外逐渐递减，以此保证医学治疗装置1700治疗的效果。 For example, as shown in the figure, when the LITT photon ablation probe is a LITT photon circumferential ablation probe 2020, the LITT photon circumferential ablation probe 2020 (including the LITT circumferential ablation probe) is disposed on the The LITT photon temperature measurement probe 2010 is disposed at the farthest position from the LITT photon circumferential ablation probe 2020 on the edge of the target object. The distance between the LITT photon circumferential ablation probe 2020 and the LITT photon temperature measurement probe 2010 is set to L dispersion . L dispersion is equal to or close to the equivalent radius of the target object. The equivalent radius here is the radius of the smallest circumscribed circle of the edge of the target object. Combined with the (circumferential) dispersion uniformity of the ablation laser of the LITT photon circumferential ablation probe 2020, the LITT photon circumferential ablation probe 2020 is set at the equivalent center, and the LITT photon temperature measurement probe 2010 is set at the target object The edge is the farthest position from the LITT photon circumferential ablation probe 2020, thus ensuring that the temperature within the entire range of the target object is higher than the preset temperature range, thereby ensuring the accuracy of temperature measurement, and the temperature is from The equivalent center gradually decreases outward to ensure the therapeutic effect of the medical treatment device 1700.
当所述LITT光子消融探针为LITT光子侧向消融探针2030时，所述LITT光子侧向消融探针2030(包括LITT侧向消融探针)设置于所述目标对象的一侧边缘，所述LITT光子测温探针2010设置于所述目标对象的相对一侧的边缘上距离所述LITT光子侧向消融探针2030最远处的位置。所述LITT光子侧向消融探针2030与所述LITT光子测温探针2010的距离设为L 侧向。L 侧向等于或接近所述目标对象的等效直径。此处所述等效直径为所述目标对象边缘的最小外接圆的直径。结合LITT光子侧向消融探针2030消融激光的特定方向的指向性及该特定方向范围内的均匀性，通过将LITT光子侧向消融探针2030设置于所述目标对象的一侧边缘，而LITT光子测温探针2010设置于所述目标对象的相对一侧的边缘上距离所述LITT光子侧向消融探针2030最远处的位置，因此保证整个目 标对象所在范围内的温度均高于预设温度范围，由此保证了测温的准确性，且温度从所述一侧向相对一侧逐渐递减，以此保证医学治疗装置1700治疗的效果。 When the LITT photon ablation probe is the LITT photon lateral ablation probe 2030, the LITT photon lateral ablation probe 2030 (including the LITT lateral ablation probe) is disposed on one edge of the target object, so The LITT photon temperature measurement probe 2010 is disposed at the farthest position from the LITT photon lateral ablation probe 2030 on the edge of the opposite side of the target object. The distance between the LITT photon lateral ablation probe 2030 and the LITT photon temperature measurement probe 2010 is set to L lateral direction . L is laterally equal to or close to the equivalent diameter of the target object. The equivalent diameter here is the diameter of the smallest circumscribed circle of the edge of the target object. Combining the directivity of the LITT photon lateral ablation probe 2030 ablation laser in a specific direction and the uniformity within the specific direction range, by setting the LITT photon lateral ablation probe 2030 on one edge of the target object, LITT The photon temperature measurement probe 2010 is disposed on the edge of the opposite side of the target object at the farthest position from the LITT photon lateral ablation probe 2030, thus ensuring that the temperature within the entire range of the target object is higher than the predetermined temperature. The temperature range is set to ensure the accuracy of temperature measurement, and the temperature gradually decreases from the side to the opposite side, thereby ensuring the treatment effect of the medical treatment device 1700.
所述目标对象的边缘可以采用图像识别或分割算法或模型对包含所述目标对象的MRI图像进行处理而确定。示例性地，典型的图像识别或分割算法可以包括卷积算法，即将图像数据与特定算子进行卷积运算，以确定图像中的边缘轮廓，其中，特定算子可以包括Roberts算子，Sobel算子、Prewitt算子以及基于拉普拉斯算子的零交叉高斯算子。在一些实施例中，边缘识别算法还可以包括Canny检测器、推进式边界学习算法((Boosted Edge Learning BEL)等视觉特征算法。The edge of the target object can be determined by using an image recognition or segmentation algorithm or model to process the MRI image containing the target object. For example, a typical image recognition or segmentation algorithm may include a convolution algorithm, that is, convolving image data with a specific operator to determine the edge contour in the image, where the specific operator may include a Roberts operator, a Sobel operator operator, Prewitt operator and zero-crossing Gaussian operator based on Laplacian operator. In some embodiments, the edge recognition algorithm may also include Canny detector, boosted edge learning algorithm (Boosted Edge Learning BEL) and other visual feature algorithms.
典型的图像识别或分割模型可以包括神经网络模型(例如，深度学习模型)、生成对抗网络(GAN)、深度置信网络(DBN)、堆叠自动编码器(SAE)、逻辑回归(LR)模型、支持向量机(SVM)模型、决策树模型、朴素贝叶斯模型、随机森林模型或受限玻尔兹曼机(RBM)、梯度提升决策树(GBDT)模型、Lambda MART模型、自适应增强模型、隐马尔可夫模型、感知器神经网络模型、Hopfield网络模型等或其任意组合。在一些实施例中，所述图像识别或分割模型识是以历史图像以其中的目标对象边缘作为样本对进行训练而得到的。Typical image recognition or segmentation models may include neural network models (e.g., deep learning models), generative adversarial networks (GAN), deep belief networks (DBN), stacked autoencoders (SAE), logistic regression (LR) models, support Vector machine (SVM) model, decision tree model, naive Bayes model, random forest model or restricted Boltzmann machine (RBM), gradient boosting decision tree (GBDT) model, Lambda MART model, adaptive enhancement model, Hidden Markov model, perceptron neural network model, Hopfield network model, etc. or any combination thereof. In some embodiments, the image recognition or segmentation model recognition is obtained by training historical images with target object edges in them as sample pairs.
LITT光子测温探针2010和LITT光子消融探针置于预设位置后，通过所述温度反馈控制单元1750、激光剂量控制单元1760、衰减器调节控制单元1770、衰减器调节单元1780以及激光功率衰减器1790，控制LITT光子测温探针2010测得的组织温度处于预设温度范围(例如，46±1℃)。以LITT光子周向消融探针2020为例，LITT光子周向消融探针2020中的LITT周向消融探针释放功率为1-8W、特征波长为1064nm的消融激光，控制LITT光子测温探针2010始终检测并基于所述温度反馈控制单元1750、激光剂量控制单元1760、衰减器调节控制单元1770、衰减器调节单元1780以及激光功率衰减器1790反馈调节所在位置处的温度处于预设温度范围。由此可以准确的保证所述目标对象整体的温度等于或高于预设温度范围，更利于LITT光子消融探针对转移性(扩散)癌症具有良好治疗效果。同时，在治疗时，可以基于OCT探针对消融病理以及细胞凋亡的实际形态做实时病理成像，进而进行病理评价，提高医学治疗装置1700的治疗效率及成功率。After the LITT photon temperature measurement probe 2010 and the LITT photon ablation probe are placed at the preset position, the temperature feedback control unit 1750, the laser dose control unit 1760, the attenuator adjustment control unit 1770, the attenuator adjustment unit 1780 and the laser power The attenuator 1790 controls the tissue temperature measured by the LITT photon thermometer probe 2010 to be in a preset temperature range (for example, 46±1°C). Taking the LITT photon circumferential ablation probe 2020 as an example, the LITT circumferential ablation probe in the LITT photon circumferential ablation probe 2020 releases an ablation laser with a power of 1-8W and a characteristic wavelength of 1064nm to control the LITT photon temperature measurement probe 2010 always detects and based on the temperature feedback control unit 1750, laser dose control unit 1760, attenuator adjustment control unit 1770, attenuator adjustment unit 1780 and laser power attenuator 1790 feedback adjustment, the temperature at the location is within the preset temperature range. This can accurately ensure that the overall temperature of the target object is equal to or higher than the preset temperature range, which is more conducive to the LITT photon ablation probe having a good therapeutic effect on metastatic (spread) cancer. At the same time, during treatment, real-time pathological imaging of ablation pathology and the actual form of cell apoptosis can be performed based on the OCT probe, and then pathological evaluation can be performed to improve the treatment efficiency and success rate of the medical treatment device 1700.
此时，临近LITT光子周向消融探针2020的肿瘤组织温度会升至近乎100℃并快速凝固坏死，而外周圆环区域为细胞48-72小时或更久时间缓慢凋亡区域。激光在组织内被持续吸收，进而产生持续热量。靠近LITT光子周向消融探针2020的较高温度导致细胞膜破裂和蛋白质持续凝固，导致受累组织持续瞬间坏死。更接近LITT光子测温探针2010的温度更低，正在引起凋亡细胞的过渡区可产生免疫原性细胞的间歇性最终趋向死亡。最终，在数小时至数天内，这些变化导致靶癌化组织将完全破坏。濒死的过渡区癌化组织细胞，经过热疗诱导细胞破裂启动癌细胞凋亡并释放抗原因子，引起人体免疫反应。At this time, the temperature of the tumor tissue adjacent to the LITT photon circumferential ablation probe 2020 will rise to nearly 100°C and rapidly coagulate and become necrotic, while the peripheral ring area will be an area where cells slowly undergo apoptosis for 48-72 hours or longer. The laser light is continuously absorbed within the tissue, thereby generating continuous heat. The higher temperature close to the LITT photon circumferential ablation probe 2020 causes cell membrane rupture and continued coagulation of proteins, resulting in continued instantaneous necrosis of the affected tissue. The lower temperatures closer to the LITT photon thermoprobe 2010, which are causing the transition zone of apoptotic cells, can produce intermittent and ultimately death of immunogenic cells. Eventually, within hours to days, these changes lead to complete destruction of the target cancerized tissue. The dying cancerous tissue cells in the transition zone undergo hyperthermia to induce cell rupture, initiate cancer cell apoptosis and release antigenic factors, triggering the human body's immune response.
本说明书实施例可能带来的有益效果包括但不限于：(1)通过比MRTI更为精准的LITT探针远端热电偶测温和/或FBG传感器测温，使得LITT的测温性能达到实时高效的反馈，充分避免了因为LITT探针远端和组织过多导致的损伤，减少术后后遗症；(2)采用LITT消融探针雕锥和斜面雕花工艺，成功制造出比原有局部散斑雕花工艺的LITT探针施源器，矢量光能分布更为均匀的LITT探针，结合上述测温机制，使得周围组织消融均匀而彻底。结合基于该均匀矢量LITT探针的组织热特性和热损伤算法，使得LITT术中对健康组织的保护，以及消融病理的消融效果，均得到了显著提升；(3)通过采用OCT病理成像机制，实时探测消融病灶的癌化病理残余，对于消融灶切缘残留的癌化病理，进行快速的补充消融。使得癌化残余和复发的可能性，降到最低；(4)通过核磁兼容马达引入两个自由度的LITT探针运动机制，完整实现高压电传感精度下的线性运动自由度和旋转运动自由度，通过驱动线性运动自由度(平移)线缆和旋转自由度(旋转)线缆，分别驱动接口平台的平移控制机构和旋转控制机构，实现MRg-LITT激光消融定位精确，运动精细可控，确保患者精准消融并完美兼容高精准度周向弥散和侧向消融LITT探针，具有巨大临床价值；(5)通过比MRTI更为精准的LITT探针远端FBG传感器测温，使得LITT的测温性能达到实时高效的反馈，充分避免了因为LITT探针远端和组织过多导致的损伤，减少术后后遗症；(6)通过采用OCT病理成像机制，实时探测消融病灶的癌化病理残余，尤其对于大尺寸病灶组织，所述OCT探针适于更长的工作距离。对于消融灶切缘残留的癌化病理，进行快速的补充消融。使得癌化残余和复发的 可能性，降到最低；(7)通过温度反馈控制单元1750、激光剂量控制单元1760、衰减器调节控制单元1770(三者可集成为处理模块)、衰减器调节单元1780，所述激光功率衰减器1790通过动态调整所述当前激光输出剂量值，使得测温元件测得的温度始终处于所述预设温度范围，结合比MRTI更为精准的LITT光子测温探针，使得医学治疗装置1700实现实时高效的动态温度反馈调整；(8)在治疗时，可以基于OCT探针对消融病理以及细胞凋亡的实际形态做实时病理成像，进而进行病理评价，提高医学治疗装置1700的治疗效率及成功率；(9)结合LITT光子周向消融探针/LITT光子侧向消融探针以及LITT光子测温探针的位置设置，结合比MRTI更为精准的LITT光子测温探针，因此保证整个目标对象所在范围内的温度均高于预设温度范围，由此保证了测温的准确性，且温度从所述等效中心向外逐渐递减，以此保证医学治疗装置1700治疗的效果。Beneficial effects that may be brought about by the embodiments of this specification include but are not limited to: (1) Temperature measurement by a remote thermocouple of the LITT probe that is more accurate than MRTI and/or temperature measurement by an FBG sensor, so that the temperature measurement performance of LITT can reach real-time Efficient feedback fully avoids damage caused by the distal end of the LITT probe and excessive tissue, reducing postoperative sequelae; (2) The LITT ablation probe is used to carve cones and bevel carving processes to successfully create localized speckles that are smaller than the original ones. The LITT probe applicator with carved craftsmanship and the LITT probe with more uniform vector light energy distribution, combined with the above-mentioned temperature measurement mechanism, enable uniform and complete ablation of surrounding tissue. Combined with the tissue thermal characteristics and thermal damage algorithm based on the uniform vector LITT probe, the protection of healthy tissue during LITT surgery and the ablation effect of pathological ablation have been significantly improved; (3) By using the OCT pathological imaging mechanism, Real-time detection of residual cancerous pathology in ablation lesions, and rapid supplementary ablation of residual cancerous pathology at the resection margin of ablation lesions. Minimizing the possibility of cancer residual and recurrence; (4) Introducing a two-degree-of-freedom LITT probe motion mechanism through a nuclear magnetic compatible motor to fully realize linear motion freedom and rotational motion with high-voltage electrical sensing accuracy Degree of freedom, by driving the linear motion freedom (translation) cable and the rotation freedom (rotation) cable, respectively driving the translation control mechanism and rotation control mechanism of the interface platform, achieving accurate positioning of MRg-LITT laser ablation and fine controllable movement , ensuring accurate ablation for patients and being perfectly compatible with high-precision circumferential diffusion and lateral ablation LITT probes, which has great clinical value; (5) Through the distal FBG sensor temperature measurement of the LITT probe that is more accurate than MRTI, the LITT The temperature measurement performance achieves real-time and efficient feedback, fully avoiding damage caused by the distal end of the LITT probe and excessive tissue, and reducing postoperative sequelae; (6) By using the OCT pathological imaging mechanism, the cancerous pathological residues of the ablation lesions can be detected in real time , especially for large-sized lesions, the OCT probe is suitable for a longer working distance. For the remaining cancerous pathology at the resection margin of the ablation lesion, rapid supplementary ablation is performed. Minimizing the possibility of cancer residual and recurrence; (7) Through the temperature feedback control unit 1750, laser dose control unit 1760, attenuator adjustment control unit 1770 (the three can be integrated into a processing module), attenuator adjustment unit 1780. The laser power attenuator 1790 dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measurement element is always within the preset temperature range, combined with the LITT photon temperature measurement probe that is more accurate than MRTI. , enabling the medical treatment device 1700 to achieve real-time and efficient dynamic temperature feedback adjustment; (8) During treatment, real-time pathological imaging of ablation pathology and the actual form of cell apoptosis can be performed based on the OCT probe, and then pathological evaluation can be performed to improve medical treatment. Treatment efficiency and success rate of device 1700; (9) Combined with the position setting of LITT photon circumferential ablation probe/LITT photon lateral ablation probe and LITT photon temperature measurement probe, combined with LITT photon temperature measurement that is more accurate than MRTI probe, thus ensuring that the temperature within the entire range of the target object is higher than the preset temperature range, thereby ensuring the accuracy of temperature measurement, and the temperature gradually decreases outward from the equivalent center, thereby ensuring that the medical treatment device 1700 healing effect.
上文已对基本概念做了描述，显然，对于本领域技术人员来说，上述详细披露仅仅作为示例，而并不构成对本说明书的限定。虽然此处并没有明确说明，本领域技术人员可能会对本说明书进行各种修改、改进和修正。该类修改、改进和修正在本说明书中被建议，所以该类修改、改进、修正仍属于本说明书示范实施例的精神和范围。The basic concepts have been described above. It is obvious to those skilled in the art that the above detailed disclosure is only an example and does not constitute a limitation of this specification. Although not explicitly stated herein, various modifications, improvements, and corrections may be made to this specification by those skilled in the art. Such modifications, improvements, and corrections are suggested in this specification, and therefore such modifications, improvements, and corrections remain within the spirit and scope of the exemplary embodiments of this specification.
同时，本说明书使用了特定词语来描述本说明书的实施例。如“一个实施例”、“一实施例”、和/或“一些实施例”意指与本说明书至少一个实施例相关的某一特征、结构或特点。因此，应强调并注意的是，本说明书中在不同位置两次或多次提及的“一实施例”或“一个实施例”或“一个替代性实施例”并不一定是指同一实施例。此外，本说明书的一个或多个实施例中的某些特征、结构或特点可以进行适当的组合。At the same time, this specification uses specific words to describe the embodiments of this specification. For example, "one embodiment," "an embodiment," and/or "some embodiments" means a certain feature, structure, or characteristic related to at least one embodiment of this specification. Therefore, it should be emphasized and noted that “one embodiment” or “an embodiment” or “an alternative embodiment” mentioned twice or more at different places in this specification does not necessarily refer to the same embodiment. . In addition, certain features, structures or characteristics in one or more embodiments of this specification may be appropriately combined.
此外，除非权利要求中明确说明，本说明书所述处理元素和序列的顺序、数字字母的使用、或其他名称的使用，并非用于限定本说明书流程和方法的顺序。尽管上述披露中通过各种示例讨论了一些目前认为有用的发明实施例，但应当理解的是，该类细节仅起到说明的目的，附加的权利要求并不仅限于披露的实施例，相反，权利要求旨在覆盖所有符合本说明书实施例实质和范围的修正和等价组合。例如，虽然以上所描述的系统组件可以通过硬件设备实现，但是也可以只通过软件的解决方案得以实现，如在现有的服务器或移动设备上安装所描述的系统。In addition, unless explicitly stated in the claims, the order of the processing elements and sequences, the use of numbers and letters, or the use of other names in this specification are not intended to limit the order of the processes and methods in this specification. Although the foregoing disclosure discusses by various examples some embodiments of the invention that are presently considered useful, it is to be understood that such details are for purposes of illustration only and that the appended claims are not limited to the disclosed embodiments. To the contrary, rights The claims are intended to cover all modifications and equivalent combinations consistent with the spirit and scope of the embodiments of this specification. For example, although the system components described above can be implemented through hardware devices, they can also be implemented through software-only solutions, such as installing the described system on an existing server or mobile device.
同理，应当注意的是，为了简化本说明书披露的表述，从而帮助对一个或多个发明实施例的理解，前文对本说明书实施例的描述中，有时会将多种特征归并至一个实施例、附图或对其的描述中。但是，这种披露方法并不意味着本说明书对象所需要的特征比权利要求中提及的特征多。实际上，实施例的特征要少于上述披露的单个实施例的全部特征。Similarly, it should be noted that, in order to simplify the expression disclosed in this specification and thereby help understand one or more embodiments of the invention, in the previous description of the embodiments of this specification, multiple features are sometimes combined into one embodiment. accompanying drawings or descriptions thereof. However, this method of disclosure does not imply that the subject matter of the description requires more features than are mentioned in the claims. In fact, embodiments may have less than all features of a single disclosed embodiment.
一些实施例中使用了描述成分、属性数量的数字，应当理解的是，此类用于实施例描述的数字，在一些示例中使用了修饰词“大约”、“近似”或“大体上”来修饰。除非另外说明，“大约”、“近似”或“大体上”表明所述数字允许有±20％的变化。相应地，在一些实施例中，说明书和权利要求中使用的数值参数均为近似值，该近似值根据个别实施例所需特点可以发生改变。在一些实施例中，数值参数应考虑规定的有效数位并采用一般位数保留的方法。尽管本说明书一些实施例中用于确认其范围广度的数值域和参数为近似值，在具体实施例中，此类数值的设定在可行范围内尽可能精确。In some embodiments, numbers are used to describe the quantities of components and properties. It should be understood that such numbers used to describe the embodiments are modified by the modifiers "about", "approximately" or "substantially" in some examples. Grooming. Unless otherwise stated, "about," "approximately," or "substantially" means that the stated number is allowed to vary by ±20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximations that may vary depending on the desired features of the individual embodiment. In some embodiments, numerical parameters should account for the specified number of significant digits and use general digit preservation methods. Although the numerical ranges and parameters used to identify the breadth of ranges in some embodiments of this specification are approximations, in specific embodiments, such numerical values are set as accurately as is feasible.
针对本说明书引用的每个专利、专利申请、专利申请公开物和其他材料，如文章、书籍、说明书、出版物、文档等，特此将其全部内容并入本说明书作为参考。与本说明书内容不一致或产生冲突的申请历史文件除外，对本说明书权利要求最广范围有限制的文件(当前或之后附加于本说明书中的)也除外。需要说明的是，如果本说明书附属材料中的描述、定义、和/或术语的使用与本说明书所述内容有不一致或冲突的地方，以本说明书的描述、定义和/或术语的使用为准。Each patent, patent application, patent application publication and other material, such as articles, books, instructions, publications, documents, etc. cited in this specification is hereby incorporated by reference into this specification in its entirety. Application history documents that are inconsistent with or conflict with the content of this specification are excluded, as are documents (currently or later appended to this specification) that limit the broadest scope of the claims in this specification. It should be noted that if there is any inconsistency or conflict between the descriptions, definitions, and/or the use of terms in the accompanying materials of this manual and the content described in this manual, the descriptions, definitions, and/or the use of terms in this manual shall prevail. .
最后，应当理解的是，本说明书中所述实施例仅用以说明本说明书实施例的原则。其他的变形也可能属于本说明书的范围。因此，作为示例而非限制，本说明书实施例的替代配置可视为与本说明书的教导一致。相应地，本说明书的实施例不仅限于本说明书明确介绍和描述的实施例Finally, it should be understood that the embodiments described in this specification are only used to illustrate the principles of the embodiments of this specification. Other variations may also fall within the scope of this specification. Accordingly, by way of example and not limitation, alternative configurations of the embodiments of this specification may be considered consistent with the teachings of this specification. Accordingly, the embodiments of this specification are not limited to those expressly introduced and described in this specification.

Claims (64)

  1. 一种医学治疗装置，其特征在于，包括：A medical treatment device, characterized in that it includes:
    磁共振成像(MRI)设备，被配置为对包括目标对象的特定区域进行成像，生成磁共振图像；激光间质热疗(LITT)设备，包括：LITT探针，基于所述磁共振图像，所述LITT探针靠近所述目标对象，并通过发射激光对所述目标对象进行治疗；和测温元件，与所述LITT探针集成为集成探针，所述测温元件被配置为获取所述目标对象的温度。a magnetic resonance imaging (MRI) device configured to image a specific region including a target object and generate a magnetic resonance image; a laser interstitial thermotherapy (LITT) device including: a LITT probe, based on the magnetic resonance image, The LITT probe is close to the target object and treats the target object by emitting laser; and a temperature measurement element is integrated with the LITT probe into an integrated probe, and the temperature measurement element is configured to obtain the The temperature of the target object.
  2. 根据权利要求1所述的医学治疗装置，其特征在于，所述测温元件包括K型热电偶，所述K型热电偶靠近所述目标对象，实时采集所述目标对象的温度变化。The medical treatment device according to claim 1 is characterized in that the temperature measuring element includes a K-type thermocouple, and the K-type thermocouple is close to the target object to collect temperature changes of the target object in real time.
  3. 根据权利要求1所述的医学治疗装置，其特征在于，所述测温元件包括光纤布拉格光栅(FBG)传感器。The medical treatment device according to claim 1, wherein the temperature measurement element includes a fiber Bragg grating (FBG) sensor.
  4. 根据权利要求3所述的医学治疗装置，其特征在于，制备所述FBG传感器的原材料需满足：材料截止波长≤1280nm，1310nm时最大衰减标准取样≤0.35dB/km，1625nm时最大衰减标准取样≤0.23dB/km，1310nm时光纤模场直径(MFD)模式场外径＝9.2±0.4μm，1550nm时MFD模式场外径＝10.4±0.5μm，1550nm时色散≤The medical treatment device according to claim 3, characterized in that the raw materials for preparing the FBG sensor need to meet: material cut-off wavelength ≤ 1280nm, maximum attenuation standard sampling at 1310nm ≤ 0.35dB/km, maximum attenuation standard sampling at 1625nm ≤ 0.23dB/km, fiber mode field diameter (MFD) mode field outer diameter = 9.2±0.4μm at 1310nm, MFD mode field outer diameter at 1550nm = 10.4±0.5μm, dispersion ≤ at 1550nm
    18ps/(nm.km)，1625nm时色散≤22ps/(nm.km)，1310nm和1550nm时点不连续性≤0.05dB，1310nm时有效折射率群1.467，1550nm时有效折射率群1.4677，1310nm时瑞丽背向散射系数-77dB，以及1550nm时瑞丽背向散射系数-82dB。18ps/(nm.km), dispersion ≤22ps/(nm.km) at 1625nm, point discontinuity at 1310nm and 1550nm ≤0.05dB, effective refractive index group at 1310nm 1.467, effective refractive index group at 1550nm 1.4677, at 1310nm The Ruili backscattering coefficient is -77dB, and the Ruili backscattering coefficient at 1550nm is -82dB.
  5. 根据权利要求3所述的医学治疗装置，其特征在于，所述FBG传感器靠近所述目标对象，确定所述目标对象的温度变化，其中，所述目标对象的温度变化是基于获取的FBG的热敏性S FBG，通过对布拉格波长漂移Δλ S与温度变化ΔT之间的关系进行校准而确定的。 The medical treatment device according to claim 3, wherein the FBG sensor is close to the target object and determines the temperature change of the target object, wherein the temperature change of the target object is based on the acquired thermal sensitivity of the FBG S FBG , determined by calibrating the relationship between the Bragg wavelength shift Δλ S and the temperature change ΔT.
  6. 根据权利要求5所述的医学治疗装置，其特征在于，对布拉格波长漂移Δλ S与温度变化ΔT之间的关系是通过将所述FBG传感器置于温度控制器内，所述温度控制器的温度间歇性变化，同时，由放大自发辐射(ASE)激光器通过环形器，到达所述FBG传感器，所述FBG传感器的反射信号通过所述环形器进入电信光谱分析仪，所述电信光谱分析仪监测所述FBG传感器的反射光谱从而确定的。 The medical treatment device according to claim 5, wherein the relationship between the Bragg wavelength shift Δλ S and the temperature change ΔT is achieved by placing the FBG sensor in a temperature controller, and the temperature of the temperature controller Intermittent changes, at the same time, the amplified spontaneous emission (ASE) laser passes through the circulator and reaches the FBG sensor. The reflected signal of the FBG sensor enters the telecommunications spectrum analyzer through the circulator, and the telecommunications spectrum analyzer monitors the The reflection spectrum of the FBG sensor is thus determined.
  7. 根据权利要求1所述的医学治疗装置，其特征在于，进一步包括：光学相干断层成像(OCT)设备，被配置为对所述目标对象进行成像，生成OCT图像。The medical treatment device according to claim 1, further comprising: an optical coherence tomography (OCT) device configured to image the target object and generate an OCT image.
  8. 根据权利要求7所述的医学治疗装置，其特征在于，所述OCT设备包括OCT探针，所述OCT探针向所述目标对象发射光信号，用以对治疗过程中的所述目标对象进行成像，所述OCT探针发射的光信号具有两种不同的中央波长。The medical treatment device according to claim 7, characterized in that the OCT device includes an OCT probe, and the OCT probe emits a light signal to the target object to perform treatment on the target object during treatment. For imaging, the optical signal emitted by the OCT probe has two different central wavelengths.
  9. 根据权利要求8所述的医学治疗装置，其特征在于，所述OCT探针与所述LITT探针和所述测温元件集成于所述集成探针。The medical treatment device according to claim 8, wherein the OCT probe, the LITT probe and the temperature measurement element are integrated into the integrated probe.
  10. 根据权利要求1所述的医学治疗装置，其特征在于，进一步包括：驱动装置，包括：平移线缆和旋转线缆， 以及平移控制机构和旋转控制机构，其中，所述平移线缆和旋转线缆分别连接于所述平移控制机构和旋转控制机构，所述平移控制机构和旋转控制机构连接于所述LITT探针，通过所述平移线缆和所述旋转线缆，分别控制所述LITT探针的平移运动和旋转运动。The medical treatment device according to claim 1, further comprising: a driving device including: a translation cable and a rotation cable, and a translation control mechanism and a rotation control mechanism, wherein the translation cable and the rotation cable Cables are respectively connected to the translation control mechanism and the rotation control mechanism. The translation control mechanism and the rotation control mechanism are connected to the LITT probe. The LITT probe is controlled by the translation cable and the rotation cable respectively. Translational and rotational motion of the needle.
  11. 根据权利要求10所述的医学治疗装置，其特征在于，所述平移控制机构包括蜗轮蜗杆组件和同步带传动组件，所述旋转控制机构包括同步带传动组件。The medical treatment device according to claim 10, wherein the translation control mechanism includes a worm gear assembly and a synchronous belt transmission assembly, and the rotation control mechanism includes a synchronous belt transmission assembly.
  12. 根据权利要求1所述的医学治疗装置，其特征在于，所述LITT探针为LITT侧向消融探针或LITT周向消融探针。The medical treatment device according to claim 1, wherein the LITT probe is a LITT lateral ablation probe or a LITT circumferential ablation probe.
  13. 根据权利要求12所述的医学治疗装置，其特征在于，所述LITT侧向消融探针包括：探针主体；和覆盖于所述探针主体端面的镀层，其中，所述探针主体的端面与探针主体的轴线呈第一夹角，所述探针主体包括针芯和位于针芯外周的硬质包层，所述镀层为贵金属靶材镀层。The medical treatment device according to claim 12, wherein the LITT lateral ablation probe includes: a probe body; and a coating covering the end surface of the probe body, wherein the end surface of the probe body It forms a first angle with the axis of the probe body. The probe body includes a needle core and a hard cladding located on the outer periphery of the needle core. The coating is a noble metal target coating.
  14. 根据权利要求13所述的医学治疗装置，其特征在于，所述镀层为双层结构，靠近所述探针主体端面的层为纯银，远离所述探针主体端面的层为一氧化硅。The medical treatment device according to claim 13, wherein the coating has a double-layer structure, the layer close to the end surface of the probe body is made of pure silver, and the layer far away from the end surface of the probe body is made of silicon monoxide.
  15. 根据权利要求13所述的医学治疗装置，其特征在于，所述LITT侧向消融探针是通过对所述探针主体的端面进行光洁化，然后对光洁化后的端面通过磁控溅射镀膜覆盖所述镀层而得到的。The medical treatment device according to claim 13, wherein the LITT lateral ablation probe is made by smoothing the end surface of the probe body, and then coating the smoothed end surface through magnetron sputtering. Obtained by covering the above-mentioned plating layer.
  16. 根据权利要求12所述的医学治疗装置，其特征在于，所述LITT侧向消融探针包括：探针主体；和连接于所述探针主体端面的透镜，其中，所述探针主体的端面与探针主体的轴线垂直，所述透镜具有第一顶角，所述探针主体包括针芯和位于针芯外周的硬质包层，所述透镜为蓝宝石透镜。The medical treatment device according to claim 12, wherein the LITT lateral ablation probe includes: a probe body; and a lens connected to an end surface of the probe body, wherein the end surface of the probe body The lens has a first vertex angle perpendicular to the axis of the probe body. The probe body includes a needle core and a hard cladding located on the outer periphery of the needle core. The lens is a sapphire lens.
  17. 根据权利要求16所述的医学治疗装置，其特征在于，所述透镜为斜切的圆柱形透镜，或斜切的半球形或半椭球形透镜。The medical treatment device according to claim 16, wherein the lens is a beveled cylindrical lens, or a beveled hemispherical or semi-ellipsoidal lens.
  18. 根据权利要求16所述的医学治疗装置，其特征在于，所述LITT侧向消融探针是通过对所述探针主体的端面进行光洁化，然后将所述探针主体和所述透镜进行熔接，并对熔接面进行火抛光而得到的。The medical treatment device according to claim 16, wherein the LITT lateral ablation probe is made by smoothing the end surface of the probe body, and then welding the probe body and the lens. , obtained by fire polishing the welded surface.
  19. 根据权利要求12所述的医学治疗装置，其特征在于，所述LITT周向消融探针包括：探针主体，所述探针主体包括锥形面，所述锥形面上设置有凹槽，所述凹槽呈花纹状均匀分布于所述锥形面，其中，所述LITT探针产生的激光从所述凹槽处出射。The medical treatment device according to claim 12, wherein the LITT circumferential ablation probe includes a probe body, the probe body includes a tapered surface, and a groove is provided on the tapered surface, The grooves are evenly distributed on the tapered surface in a pattern shape, and the laser light generated by the LITT probe is emitted from the grooves.
  20. 根据权利要求19所述的医学治疗装置，其特征在于，所述锥形面的直径由初始直径逐渐缩小至预设直径，所述初始直径为630μm，所述预设直径为100μm。The medical treatment device according to claim 19, wherein the diameter of the tapered surface gradually decreases from an initial diameter to a preset diameter, the initial diameter is 630 μm, and the preset diameter is 100 μm.
  21. 根据权利要求19所述的医学治疗装置，其特征在于，所述花纹包括单螺纹形状，交叉螺纹形状或菱形网格形状或其组合。The medical treatment device according to claim 19, wherein the pattern includes a single thread shape, a cross thread shape, a rhombus grid shape or a combination thereof.
  22. 根据权利要求19所述的医学治疗装置，其特征在于，所述锥形面通过执行如下操作形成：将待雕锥工件的 两端分别固定于滑轨和固定器件；激光器控制器控制激光器发射激光，所述激光的功率为30W，波长为10600nm，所述激光经激光功率衰减器衰减至6.6到11.2W，衰减处理后的激光经衍射分束透镜单元分为两束激光，所述两束激光功率相等，所述两束激光经过聚焦透镜单元聚焦至待雕锥工件表面；以及运动驱动控制器控制运动驱动器，驱动所述待雕锥工件运动。The medical treatment device according to claim 19 is characterized in that the conical surface is formed by performing the following operations: fixing the two ends of the workpiece to be engraved to the slide rail and the fixing device respectively; the laser controller controls the laser to emit laser, the power of the laser is 30W, the wavelength is 10600nm, the laser is attenuated to 6.6 to 11.2W by the laser power attenuator, the attenuated laser is divided into two laser beams by the diffraction beam splitting lens unit, the two laser beams have equal power, and the two laser beams are focused to the surface of the workpiece to be engraved by the focusing lens unit; and the motion drive controller controls the motion driver to drive the workpiece to be engraved to move.
  23. 根据权利要求19所述的医学治疗装置，其特征在于，所述呈花纹状均匀分布于所述锥形面的凹槽通过执行如下操作形成：将待雕花工件的两端分别固定于滑轨和固定器件；激光器控制器控制激光器发射激光，所述激光的功率为30W，波长为10600nm，所述激光经透镜组，聚焦至所述待雕花工件表面，所述透镜组包括第一凹透镜、第一凸透镜和第二凹透镜，所述第一凹透镜和第一凸透镜用于将激光束的直径扩展到第一直径，第二凹透镜用于将第一直径的激光束聚焦至待雕花工件表面，形成光斑，所述光斑直径为45μm；以及运动驱动控制器控制运动驱动器，驱动所述待雕花工件运动。The medical treatment device according to claim 19 is characterized in that the grooves uniformly distributed on the conical surface in a pattern are formed by performing the following operations: fixing the two ends of the workpiece to be carved to the slide rail and the fixing device respectively; the laser controller controls the laser to emit laser, the power of the laser is 30W, the wavelength is 10600nm, the laser is focused to the surface of the workpiece to be carved through a lens group, the lens group includes a first concave lens, a first convex lens and a second concave lens, the first concave lens and the first convex lens are used to expand the diameter of the laser beam to a first diameter, the second concave lens is used to focus the laser beam of the first diameter to the surface of the workpiece to be carved to form a light spot, the diameter of the light spot is 45μm; and the motion drive controller controls the motion driver to drive the workpiece to be carved to move.
  24. 根据权利要求19所述的医学治疗装置，其特征在于，所述LITT周向消融探针发出的激光的空间强度分布通过如下方式获得：获取激光测量传感器输出的信号，生成所述LITT周向消融探针发出的激光的特定方位的极性强度，其中，所述LITT周向消融探针连接发射激光波长为632.8nm的氦氖激光器，所述激光测量传感器与所述LITT周向消融探针之间设置有狭缝光阑，所述狭缝光阑的狭缝尺寸为0.3mm；以及运动驱动控制器控制运动驱动器，以驱动所述光阑及激光测量传感器沿所述LITT周向消融探针的锥形面作周向和轴向运动，以所述获得LITT周向消融探针发出的激光的空间强度分布，其中，所述光阑与所述激光测量传感器固定连接于所述运动驱动器。The medical treatment device according to claim 19, wherein the spatial intensity distribution of the laser emitted by the LITT circumferential ablation probe is obtained in the following manner: acquiring a signal output by a laser measurement sensor and generating the LITT circumferential ablation The polar intensity of the laser emitted by the probe in a specific direction, wherein the LITT circumferential ablation probe is connected to a helium-neon laser that emits a laser wavelength of 632.8 nm, and the laser measurement sensor is connected to the LITT circumferential ablation probe. A slit diaphragm is provided, the slit size of the slit diaphragm is 0.3mm; and the motion drive controller controls the motion driver to drive the aperture and the laser measurement sensor to ablate the probe along the LITT circumferential direction. The tapered surface moves circumferentially and axially to obtain the spatial intensity distribution of the laser light emitted by the LITT circumferential ablation probe, wherein the aperture and the laser measurement sensor are fixedly connected to the motion driver.
  25. 一种激光间质热疗(LITT)侧向消融探针，用于LITT设备，其特征在于，所述LITT侧向消融探针包括：探针主体；和覆盖于所述探针主体端面的镀层，其中，所述探针主体的端面与探针主体的轴线呈第一夹角，所述探针主体包括针芯和位于针芯外周的硬质包层，所述针芯由纯二氧化硅材料制成，所述硬质包层由技术增强型包层二氧化硅(TECS)材料制成，所述镀层为贵金属靶材镀层。A laser interstitial thermotherapy (LITT) lateral ablation probe for LITT equipment, characterized in that the LITT lateral ablation probe includes: a probe body; and a coating covering the end surface of the probe body , wherein the end face of the probe body forms a first angle with the axis of the probe body. The probe body includes a needle core and a hard cladding located on the outer periphery of the needle core. The needle core is made of pure silica. The hard cladding is made of technology-enhanced cladding silica (TECS) material, and the coating is precious metal target coating.
  26. 根据权利要求25所述的LITT侧向消融探针，其特征在于，所述镀层为双层结构，靠近所述探针主体端面的层为纯银，远离所述探针主体端面的层为一氧化硅。The LITT lateral ablation probe according to claim 25, wherein the coating has a double-layer structure, the layer close to the end surface of the probe body is pure silver, and the layer far away from the end surface of the probe body is pure silver. Silicon oxide.
  27. 根据权利要求26所述的LITT侧向消融探针，其特征在于，所述靠近所述探针主体端面的层的厚度为100nm，远离所述探针主体端面的层的厚度为150nm，所述镀层与所述探针主体的轴线呈第二夹角为，所述第二夹角为47°。The LITT lateral ablation probe according to claim 26, wherein the thickness of the layer close to the end surface of the probe body is 100 nm, and the thickness of the layer far away from the end surface of the probe body is 150 nm. The plating layer forms a second included angle with the axis of the probe body, and the second included angle is 47°.
  28. 根据权利要求27所述的LITT侧向消融探针，其特征在于，所述LITT侧向消融探针是通过对所述探针主体的端面进行光洁化，然后对光洁化后的端面通过磁控溅射镀膜覆盖所述镀层而得到的。The LITT lateral ablation probe according to claim 27, wherein the LITT lateral ablation probe is made by polishing the end face of the probe body, and then passing the polished end face through magnetic control. The sputter coating is obtained by covering the coating.
  29. 一种激光间质热疗(LITT)侧向消融探针，用于LITT设备，其特征在于，所述LITT侧向消融探针包括：探针主体；和连接于所述探针主体端面的透镜，其中，所述探针主体的端面与探针主体的轴线垂直，所述透镜具有第一顶角，所述探针主体包括针芯和位于针芯外周的硬质包层，所述针芯由纯二氧化硅材料制成，所述硬质包层由TECS材料制成，所述透镜为蓝宝石透镜。A laser interstitial thermal therapy (LITT) lateral ablation probe, used in a LITT device, characterized in that the LITT lateral ablation probe comprises: a probe body; and a lens connected to the end face of the probe body, wherein the end face of the probe body is perpendicular to the axis of the probe body, the lens has a first vertex angle, the probe body comprises a needle core and a hard cladding located on the periphery of the needle core, the needle core is made of pure silica material, the hard cladding is made of TECS material, and the lens is a sapphire lens.
  30. 根据权利要求29所述的LITT侧向消融探针，其特征在于，所述透镜为斜切的圆柱形透镜，或斜切的半球形或半椭球形透镜。The LITT lateral ablation probe according to claim 29, wherein the lens is a beveled cylindrical lens, or a beveled hemispherical or semi-ellipsoidal lens.
  31. 根据权利要求29所述的LITT侧向消融探针，其特征在于，所述LITT侧向消融探针是通过对所述探针主体的端面进行光洁化，然后将所述探针主体和所述透镜进行熔接，并对熔接面进行火抛光而得到的。The LITT lateral ablation probe according to claim 29, characterized in that, the LITT lateral ablation probe is made by smoothing the end surface of the probe body, and then connecting the probe body and the The lens is welded and the welded surface is fire polished.
  32. 一种激光间质热疗(LITT)周向消融探针，用于LITT设备，其特征在于，所述LITT探针周向消融包括：探针主体，所述探针主体包括锥形面，所述锥形面上设置有凹槽，所述凹槽呈花纹状均匀分布于所述锥形面，其中，所述LITT探针产生的激光从所述凹槽处出射。A laser interstitial thermal therapy (LITT) circumferential ablation probe, used in a LITT device, characterized in that the LITT probe circumferential ablation comprises: a probe body, the probe body comprises a conical surface, the conical surface is provided with grooves, the grooves are evenly distributed on the conical surface in a pattern, wherein the laser generated by the LITT probe is emitted from the grooves.
  33. 根据权利要求32所述的LITT周向消融探针，其特征在于，所述锥形面的直径由初始直径逐渐缩小至预设直径，所述初始直径为630μm，所述预设直径为100μm。The LITT circumferential ablation probe according to claim 32, wherein the diameter of the tapered surface gradually decreases from an initial diameter to a preset diameter, the initial diameter is 630 μm, and the preset diameter is 100 μm.
  34. 根据权利要求32所述的LITT周向消融探针，其特征在于，所述花纹包括单螺纹形状，交叉螺纹形状或菱形网格形状或其组合。The LITT circumferential ablation probe according to claim 32, wherein the pattern includes a single thread shape, a cross thread shape, a rhombus grid shape or a combination thereof.
  35. 根据权利要求32-34中任一项所述的LITT周向消融探针，其特征在于，所述锥形面通过执行如下操作形成：将待雕锥工件的两端分别固定于滑轨和固定器件；激光器控制器控制激光器发射激光，所述激光的功率为30W，波长为10600nm，所述激光经激光功率衰减器衰减至6.6到11.2W，衰减处理后的激光经衍射分束透镜单元分为两束激光，所述两束激光功率相等，所述两束激光经过聚焦透镜单元聚焦至待雕锥工件表面；以及运动驱动控制器控制运动驱动器，驱动所述待雕锥工件运动。The LITT circumferential ablation probe according to any one of claims 32 to 34, wherein the tapered surface is formed by performing the following operations: fixing both ends of the cone workpiece to be carved to the slide rail and Device; the laser controller controls the laser to emit laser. The power of the laser is 30W and the wavelength is 10600nm. The laser is attenuated to 6.6 to 11.2W through the laser power attenuator. The attenuated laser is divided into parts through the diffraction beam splitting lens unit. Two laser beams, the power of the two laser beams are equal, the two laser beams are focused to the surface of the cone workpiece to be carved through the focusing lens unit; and the motion drive controller controls the motion driver to drive the movement of the cone workpiece to be carved.
  36. 根据权利要求32-34中任一项所述的LITT周向消融探针，其特征在于，所述呈花纹状均匀分布于所述锥形面的凹槽通过执行如下操作形成：将待雕花工件的两端分别固定于滑轨和固定器件；激光器控制器控制激光器发射激光，所述激光的功率为30W，波长为10600nm，所述激光经透镜组，聚焦至所述待雕花工件表面，所述透镜组包括第一凹透镜、第一凸透镜和第二凹透镜，所述第一凹透镜和第一凸透镜用于将激光束的直径扩展到第一直径，第二凹透镜用于将第一直径的激光束聚焦至待雕花工件表面，形成光斑，所述光斑直径为45μm；以及运动驱动控制器控制运动驱动器，驱动所述待雕花工件运动。The LITT circumferential ablation probe according to any one of claims 32 to 34, wherein the grooves evenly distributed on the tapered surface in a pattern are formed by performing the following operations: placing the workpiece to be carved Both ends are fixed on the slide rails and fixed devices respectively; the laser controller controls the laser to emit laser, the power of the laser is 30W, the wavelength is 10600nm, the laser is focused to the surface of the workpiece to be carved through the lens group, the The lens group includes a first concave lens, a first convex lens and a second concave lens. The first concave lens and the first convex lens are used to expand the diameter of the laser beam to a first diameter. The second concave lens is used to focus the laser beam of the first diameter. A light spot is formed on the surface of the workpiece to be carved, and the diameter of the light spot is 45 μm; and the motion drive controller controls the motion driver to drive the movement of the workpiece to be carved.
  37. 根据权利要求32-34中任一项所述的LITT周向消融探针，其特征在于，所述LITT周向消融探针发出的激光的空间强度分布通过如下方式获得：The LITT circumferential ablation probe according to any one of claims 32 to 34, characterized in that the spatial intensity distribution of the laser emitted by the LITT circumferential ablation probe is obtained in the following manner:
    获取激光测量传感器输出的信号，生成所述LITT周向消融探针发出的激光的特定方位的极性强度，其中，所述LITT周向消融探针连接发射激光波长为632.8nm的氦氖激光器，所述激光测量传感器与所述LITT周向消融探针之间设置有狭缝光阑，所述狭缝光阑的狭缝尺寸为0.3mm；以及Obtain the signal output by the laser measurement sensor and generate the polar intensity of the laser light emitted by the LITT circumferential ablation probe at a specific direction, wherein the LITT circumferential ablation probe is connected to a helium-neon laser that emits a laser wavelength of 632.8 nm, A slit diaphragm is provided between the laser measurement sensor and the LITT circumferential ablation probe, and the slit diaphragm has a slit size of 0.3 mm; and
    运动驱动控制器控制运动驱动器，以驱动所述光阑及激光测量传感器沿所述LITT周向消融探针的锥形面作周向和轴向运动，以所述获得LITT周向消融探针发出的激光的空间强度分布，其中，所述光阑与所述激光测量传感器固定连接于所述运动驱动器。The motion drive controller controls the motion driver to drive the aperture and the laser measurement sensor to move circumferentially and axially along the tapered surface of the LITT circumferential ablation probe to obtain the emission of the LITT circumferential ablation probe. The spatial intensity distribution of the laser, wherein the aperture and the laser measurement sensor are fixedly connected to the motion driver.
  38. 一种制备光纤布拉格光栅(FBG)传感器的方法，其特征在于，所述方法包括：A method of preparing a fiber Bragg grating (FBG) sensor, characterized in that the method includes:
    将制备所述FBG传感器的原材料固定于固定器件，所述固定器件固定连接于运动驱动器；Fix the raw materials for preparing the FBG sensor to a fixing device, and the fixing device is fixedly connected to the motion driver;
    由激光器控制器控制激光器发射激光，所述激光依次经过光束校正装置，狭缝光阑，紫外镀膜透镜和相位掩膜后，在所述原材料表面产生条带状光斑；以及由运动驱动控制器控制运动驱动器，驱动所述原材料运动，在所述原材料运动过程中，通过所述激光照射所述原材料，从而形成所述FBG传感器。The laser controller controls the laser to emit laser, and the laser passes through the beam correction device, the slit aperture, the UV-coated lens and the phase mask in sequence to generate a strip-shaped light spot on the surface of the raw material; and the motion drive controller controls the motion drive to drive the raw material to move. During the movement of the raw material, the laser irradiates the raw material to form the FBG sensor.
  39. 根据权利要求38所示的制备FBG传感器的方法，其特征在于，所述激光器为248nm特征波长的准分子脉冲激光器，所述激光器产生的激光为248nm中央波长，脉冲持续时间15ns的矩形平顶光束。The method for preparing an FBG sensor according to claim 38 is characterized in that the laser is an excimer pulse laser with a characteristic wavelength of 248 nm, and the laser generated by the laser is a rectangular flat-top beam with a central wavelength of 248 nm and a pulse duration of 15 ns.
  40. 根据权利要求38所示的制备FBG传感器的方法，其特征在于，The method for preparing an FBG sensor according to claim 38, characterized in that:
    所述光束校正装置包括两个248nm特征波长准分子激光45°线镜，The beam correction device includes two 248nm characteristic wavelength excimer laser 45° line mirrors,
    所述狭缝光阑包括4.5mm宽度可调的机械狭缝装置，The slit aperture includes a mechanical slit device with an adjustable width of 4.5 mm.
    所述紫外镀膜透镜包括245-440nm特征波长紫外镀膜熔融石英平凸圆柱透镜，The UV-coated lens includes a 245-440nm characteristic wavelength UV-coated fused silica plano-convex cylindrical lens,
    所述相位掩膜包括紫外辐照248nm特征波长1460-1600nm超带宽相位掩膜，The phase mask includes ultraviolet radiation 248nm characteristic wavelength 1460-1600nm ultra-bandwidth phase mask,
    所述条带状光斑的宽度为20mm，高度为32.4μm。The strip-shaped light spot has a width of 20 mm and a height of 32.4 μm.
  41. 根据权利要求38所示的制备FBG传感器的方法，其特征在于，制备所述FBG传感器的原材料需满足：材料截止波长≤1280nm，1310nm时最大衰减标准取样≤0.35dB/km，1625nm时最大衰减标准取样≤0.23dB/km，1310nm时光纤模场直径(MFD)模式场外径＝9.2±0.4μm，1550nm时MFD模式场外径＝10.4±0.5μm，1550nm时色散≤18ps/(nm.km)，1625nm时色散≤22ps/(nm.km)，1310nm和1550nm时点不连续性≤0.05dB，1310nm时有效折射率群1.467，1550nm时有效折射率群1.4677，1310nm时瑞丽背向散射系数-77dB，以及1550nm时瑞丽背向散射系数-82dB。The method for preparing an FBG sensor according to claim 38, characterized in that the raw materials for preparing the FBG sensor need to meet: material cutoff wavelength ≤ 1280nm, maximum attenuation standard sampling at 1310nm ≤ 0.35dB/km, maximum attenuation standard at 1625nm Sampling ≤0.23dB/km, fiber mode field diameter (MFD) mode field outer diameter=9.2±0.4μm at 1310nm, MFD mode field outer diameter=10.4±0.5μm at 1550nm, dispersion ≤18ps/(nm.km) at 1550nm , dispersion at 1625nm ≤ 22ps/(nm.km), point discontinuity at 1310nm and 1550nm ≤ 0.05dB, effective refractive index group at 1310nm 1.467, effective refractive index group at 1550nm 1.4677, Ruili backscattering coefficient at 1310nm -77dB , and the Ruili backscattering coefficient at 1550nm is -82dB.
  42. 一种医学治疗装置，其特征在于，包括：A medical treatment device, characterized in that it includes:
    磁共振成像(MRI)设备，被配置为对包括目标对象的特定区域进行成像，生成磁共振图像；a magnetic resonance imaging (MRI) device configured to image a specific area including a target object to generate a magnetic resonance image;
    激光间质热疗(LITT)设备，包括：LITT探针，基于所述磁共振图像，所述LITT探针靠近所述目标对象，并通过发射激光对所述目标对象进行治疗；和光纤布拉格光栅(FBG)传感器，被配置为获取所述目标对象的温度，其中，所述FBG传感器是根据权利要求38-41中任意一项所述的制备FBG传感器的方法制备而成的。Laser interstitial thermotherapy (LITT) equipment, including: a LITT probe that is close to the target object and treats the target object by emitting laser light based on the magnetic resonance image; and a fiber Bragg grating (FBG) sensor configured to obtain the temperature of the target object, wherein the FBG sensor is prepared according to the method of preparing an FBG sensor according to any one of claims 38-41.
  43. 根据权利要求42所述的医学治疗装置，其特征在于，所述FBG传感器靠近所述目标对象，确定所述目标对象的温度变化，其中，所述目标对象的温度变化是基于获取的FBG的热敏性S FBG，通过对布拉格波长漂移Δλ S与温度变化ΔT之间的关系进行校准而确定的。 The medical treatment device according to claim 42, wherein the FBG sensor is close to the target object to determine the temperature change of the target object, wherein the temperature change of the target object is based on the acquired thermal sensitivity of the FBG S FBG , determined by calibrating the relationship between the Bragg wavelength shift Δλ S and the temperature change ΔT.
  44. 根据权利要求43所述的医学治疗装置，其特征在于，对布拉格波长漂移Δλ S与温度变化ΔT之间的关系是通过将所述FBG传感器置于温度控制器内，所述温度控制器的温度间歇性变化，同时，由放大自发辐射(ASE)激光器通过环形器，到达所述FBG传感器，所述FBG传感器的反射信号通过所述环形器进入电信光谱分析仪，所述电信光谱分析仪监测所述FBG传感器的反射光谱从而确定的。 The medical treatment device according to claim 43, wherein the relationship between the Bragg wavelength drift Δλ S and the temperature change ΔT is achieved by placing the FBG sensor in a temperature controller, and the temperature of the temperature controller Intermittent changes, at the same time, the amplified spontaneous emission (ASE) laser passes through the circulator and reaches the FBG sensor. The reflected signal of the FBG sensor enters the telecommunications spectrum analyzer through the circulator, and the telecommunications spectrum analyzer monitors the The reflection spectrum of the FBG sensor is thus determined.
  45. 一种光学相干断层成像(OCT)探针，其特征在于，包括：An optical coherence tomography (OCT) probe, characterized by including:
    输入端口，被配置为将光源发出的光束输入至所述OCT探针；An input port configured to input the light beam emitted by the light source to the OCT probe;
    第一透镜，被配置为对入射所述OCT探针的光束进行扩束；A first lens configured to expand the light beam incident on the OCT probe;
    第二透镜，设置于所述第一透镜的后级，被配置为对出射所述第一透镜的光束进行消色差和聚焦；和光束偏转单元，设置于所述第二透镜的后级，被配置为对出射所述第二透镜的光束进行偏转出射，所述光束偏转单元包括针芯和位于针芯外周的硬质包层，所述光束偏转单元包括斜切端面，所述斜切端面涂覆有金属镀层。A second lens, disposed at the downstream stage of the first lens, is configured to achromatize and focus the light beam exiting the first lens; and a beam deflection unit, disposed at the downstream stage of the second lens, is Configured to deflect the light beam exiting the second lens, the light beam deflection unit includes a needle core and a hard cladding located on the outer periphery of the needle core, the light beam deflection unit includes a chamfered end surface, and the chamfered end surface is coated with Covered with metal plating.
  46. 根据权利要求45所述的OCT探针，其特征在于，所述第一透镜为无芯透镜，所述OCT探针的焦距及光斑大 小与所述无芯透镜的长度相关。The OCT probe according to claim 45, wherein the first lens is a coreless lens, and the focal length and spot size of the OCT probe are related to the length of the coreless lens.
  47. 根据权利要求45所述的OCT探针，其特征在于，所述第二透镜为微平凸球面柱透镜，所述微平凸球面柱透镜沿轴向的始端为平面，末端为球面，所述平面的角度为0°或8°，所述球面的曲率为-1.8mm，所述微平凸球面柱透镜的柱面直径为560μm。The OCT probe according to claim 45, wherein the second lens is a micro-plano-convex spherical cylindrical lens, the starting end of the micro-plano-convex spherical cylindrical lens along the axial direction is a plane, and the end is a spherical surface, and the The angle of the plane is 0° or 8°, the curvature of the spherical surface is -1.8mm, and the cylindrical diameter of the micro plano-convex spherical cylindrical lens is 560 μm.
  48. 根据权利要求45所述的OCT探针，其特征在于，所述光束偏转单元的截断轴向柱体长度为5μm。The OCT probe according to claim 45, wherein the beam deflection unit has a truncated axial cylinder length of 5 μm.
  49. 根据权利要求45所述的OCT探针，其特征在于，进一步包括：弹簧扭力线圈，设置于所述OCT探针前端；光学套管，所述第一透镜、第二透镜、光束偏转单元及所述弹簧扭力线圈容纳于所述光学套管中；和填充体，填充于所述光学套管内部，使所述第一透镜、第二透镜、光束偏转单元相对于所述光学套管固定。The OCT probe according to claim 45 is characterized in that it further includes: a spring torsion coil, which is arranged at the front end of the OCT probe; an optical sleeve, in which the first lens, the second lens, the beam deflection unit and the spring torsion coil are accommodated; and a filling body, which is filled inside the optical sleeve to fix the first lens, the second lens and the beam deflection unit relative to the optical sleeve.
  50. 一种医学治疗装置，其特征在于，包括：A medical treatment device, characterized in that it includes:
    磁共振成像(MRI)设备，被配置为对包括目标对象的特定区域进行成像，生成磁共振图像；激光间质热疗(LITT)设备，包括：LITT探针，基于所述磁共振图像，所述LITT探针靠近所述目标对象，并通过发射激光对所述目标对象进行治疗；和光学相干断层成像(OCT)设备，被配置为对所述目标对象进行成像，所述OCT设备包括根据权利要求45-49中任意一项所述的OCT探针。a magnetic resonance imaging (MRI) device configured to image a specific region including a target object and generate a magnetic resonance image; a laser interstitial thermotherapy (LITT) device including: a LITT probe, based on the magnetic resonance image, the LITT probe is positioned close to the target object and treats the target object by emitting laser light; and an optical coherence tomography (OCT) device configured to image the target object, the OCT device comprising: The OCT probe according to any one of claims 45-49.
  51. 一种医学治疗装置，其特征在于，包括：A medical treatment device, characterized in that it includes:
    磁共振成像(MRI)设备，被配置为对包括目标对象的特定区域进行成像，生成磁共振图像；a magnetic resonance imaging (MRI) device configured to image a specific area including a target object to generate a magnetic resonance image;
    激光间质热疗(LITT)设备，包括：LITT探针，基于所述磁共振图像，所述LITT探针靠近所述目标对象，并通过发射激光对所述目标对象进行治疗；和测温元件，被配置为获取所述目标对象边缘上特定位置的温度，所述特定位置为所述目标对象边缘上距离所述LITT探针最远的位置。Laser interstitial thermotherapy (LITT) equipment, including: a LITT probe, based on the magnetic resonance image, the LITT probe is close to the target object and treats the target object by emitting laser; and a temperature measurement element , is configured to obtain the temperature of a specific position on the edge of the target object, where the specific position is the farthest position from the LITT probe on the edge of the target object.
  52. 根据权利要求51所述的医学治疗装置，其特征在于，所述测温元件包括LITT光子测温探针。The medical treatment device according to claim 51, wherein the temperature measurement element includes a LITT photon temperature measurement probe.
  53. 根据权利要求51所述的医学治疗装置，其特征在于，进一步包括处理模块，所述处理模块被配置为：The medical treatment device according to claim 51, further comprising a processing module configured to:
    当所述测温元件测得的温度超出预设温度范围时，基于测得的温度与所述预设温度范围的差值，确定所述LITT设备的目标激光输出剂量值，使得所述测温元件测得的温度处于所述预设温度范围。When the temperature measured by the temperature measuring element exceeds the preset temperature range, the target laser output dose value of the LITT device is determined based on the difference between the measured temperature and the preset temperature range, so that the temperature measurement The temperature measured by the component is within the preset temperature range.
  54. 根据权利要求53所述的医学治疗装置，其特征在于，进一步包括激光功率衰减器，被配置为将当前激光输出剂量值调整为所述目标激光输出剂量值。The medical treatment device according to claim 53, further comprising a laser power attenuator configured to adjust the current laser output dose value to the target laser output dose value.
  55. 根据权利要求54所述的医学治疗装置，其特征在于，所述激光功率衰减器通过动态调整所述当前激光输出剂量值，使得测温元件测得的温度始终处于所述预设温度范围。The medical treatment device according to claim 54, wherein the laser power attenuator dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measuring element is always within the preset temperature range.
  56. 根据权利要求53所述的医学治疗装置，其特征在于，所述预设温度范围为46±1℃。The medical treatment device according to claim 53, wherein the preset temperature range is 46±1°C.
  57. 根据权利要求51所述的医学治疗装置，其特征在于，所述LITT探针为LITT侧向消融探针或LITT周向消融探针。The medical treatment device according to claim 51, wherein the LITT probe is a LITT lateral ablation probe or a LITT circumferential ablation probe.
  58. 根据权利要求57所述的医学治疗装置，其特征在于，所述LITT周向消融探针设置于所述目标对象的等效中心，所述测温元件设置于所述目标对象边缘上距离所述LITT周向消融探针最远处的位置，所述LITT周向消融探针与所述测温元件的距离等于或接近所述目标对象的等效半径。The medical treatment device according to claim 57, wherein the LITT circumferential ablation probe is disposed at the equivalent center of the target object, and the temperature measurement element is disposed on the edge of the target object at a distance of The farthest position of the LITT circumferential ablation probe, and the distance between the LITT circumferential ablation probe and the temperature measurement element is equal to or close to the equivalent radius of the target object.
  59. 根据权利要求57所述的医学治疗装置，其特征在于，所述LITT侧向消融探针设置于所述目标对象的一侧边缘，所述测温元件设置于所述目标对象的相对一侧的边缘上距离所述LITT侧向消融探针最远处的位置，所述LITT侧向消融探针与所述测温元件的距离等于或接近所述目标对象的等效直径。The medical treatment device according to claim 57, wherein the LITT lateral ablation probe is disposed on one edge of the target object, and the temperature measurement element is disposed on the opposite side of the target object. At the farthest position on the edge from the LITT lateral ablation probe, the distance between the LITT lateral ablation probe and the temperature measurement element is equal to or close to the equivalent diameter of the target object.
  60. 根据权利要求51所述的医学治疗装置，其特征在于，进一步包括：The medical treatment device according to claim 51, further comprising:
    光学相干断层成像(OCT)设备，被配置为对所述目标对象进行成像，生成OCT图像。An optical coherence tomography (OCT) device is configured to image the target object and generate an OCT image.
  61. 根据权利要求60所述的医学治疗装置，其特征在于，所述OCT设备包括OCT探针，所述OCT探针向所述目标对象发射光信号，用以对治疗过程中的所述目标对象进行成像，所述OCT探针发射的光信号具有两种不同的中央波长。The medical treatment device according to claim 60, characterized in that the OCT device includes an OCT probe, and the OCT probe emits a light signal to the target object to perform treatment on the target object during treatment. For imaging, the optical signal emitted by the OCT probe has two different central wavelengths.
  62. 根据权利要求51所述的医学治疗装置，其特征在于，进一步包括：The medical treatment device according to claim 51, further comprising:
    第一驱动装置，耦合于所述LITT探针，并控制所述LITT探针的平移运动和旋转运动；和a first driving device coupled to the LITT probe and controlling the translational movement and rotational movement of the LITT probe; and
    第二驱动装置，耦合于所述测温元件，并控制所述测温元件的平移运动。The second driving device is coupled to the temperature measuring element and controls the translational movement of the temperature measuring element.
  63. 根据权利要求62所述的医学治疗装置，其特征在于，所述第一驱动装置包括：The medical treatment device according to claim 62, wherein the first driving device includes:
    第一平移线缆和第一旋转线缆，以及a first translation cable and a first rotation cable, and
    第一平移控制机构和第一旋转控制机构，其中，a first translation control mechanism and a first rotation control mechanism, wherein,
    所述第一平移线缆和第一旋转线缆分别连接于所述第一平移控制机构和第一旋转控制机构，所述第一平移控制机构和第一旋转控制机构连接于所述LITT探针，通过所述第一平移线缆和所述第一旋转线缆，分别控制所述LITT探针的平移运动和旋转运动。The first translation cable and the first rotation cable are connected to the first translation control mechanism and the first rotation control mechanism respectively, and the first translation control mechanism and the first rotation control mechanism are connected to the LITT probe. , through the first translation cable and the first rotation cable, the translation movement and rotation movement of the LITT probe are controlled respectively.
  64. 根据权利要求62所述的医学治疗装置，其特征在于，所述第二驱动装置包括：The medical treatment device according to claim 62, wherein the second driving device includes:
    第二平移线缆；和a second translation cable; and
    第二平移控制机构，其中，所述第二平移线缆连接于所述第二平移控制机构，所述第二平移控制机构连接于所述测温元件，通过所述第二平移线缆控制所述测温元件的平移运动。A second translation control mechanism, wherein the second translation cable is connected to the second translation control mechanism, the second translation control mechanism is connected to the temperature measuring element, and the second translation cable is used to control the second translation control mechanism. Describe the translational movement of the temperature measuring element.
PCT/CN2022/123856 2022-07-02 2022-10-08 Medical treatment device and treatment probe WO2024060314A1 (en)

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